+

WO2001035088A1 - Dispositifs microfluidiques avec detection electrochimique a film epais - Google Patents

Dispositifs microfluidiques avec detection electrochimique a film epais Download PDF

Info

Publication number
WO2001035088A1
WO2001035088A1 PCT/US2000/030422 US0030422W WO0135088A1 WO 2001035088 A1 WO2001035088 A1 WO 2001035088A1 US 0030422 W US0030422 W US 0030422W WO 0135088 A1 WO0135088 A1 WO 0135088A1
Authority
WO
WIPO (PCT)
Prior art keywords
separation
thick
detection
substrate
channel
Prior art date
Application number
PCT/US2000/030422
Other languages
English (en)
Inventor
Joseph Wang
Baomin Tian
Eskil Sahlin
Original Assignee
New Mexico State University Technology Transfer Corporation
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by New Mexico State University Technology Transfer Corporation filed Critical New Mexico State University Technology Transfer Corporation
Priority to AU22490/01A priority Critical patent/AU2249001A/en
Publication of WO2001035088A1 publication Critical patent/WO2001035088A1/fr

Links

Classifications

    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N27/00—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means
    • G01N27/26—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating electrochemical variables; by using electrolysis or electrophoresis
    • G01N27/416—Systems
    • G01N27/447—Systems using electrophoresis
    • G01N27/44704—Details; Accessories
    • G01N27/44717—Arrangements for investigating the separated zones, e.g. localising zones
    • G01N27/4473—Arrangements for investigating the separated zones, e.g. localising zones by electric means
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N27/00—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means
    • G01N27/26—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating electrochemical variables; by using electrolysis or electrophoresis
    • G01N27/416—Systems
    • G01N27/447—Systems using electrophoresis
    • G01N27/44756—Apparatus specially adapted therefor
    • G01N27/44791—Microapparatus

Definitions

  • Electrochemical Detectors filed on November 5, 1999, and the specification thereof is incorporated herein by reference.
  • the present invention relates to electrochemical detection of analytes using thick-film electrodes, including screen-printed thick-film electrodes, in microfluidic devices, including separation devices such as capillary electrophoresis microsystems.
  • Microscale separation devices particularly chip-based, micromachined capillary electrophoresis (CE) systems
  • CE capillary electrophoresis
  • These miniaturized devices present the ability to shrink conventional "bench-top" separation systems while providing major advantages in speed, cost, portability, and solvent/sample consumption.
  • Much of the work on CE microchips uses laser-fluorescence detection. Yet, such detection requires a large and expensive supporting optical system, and is limited to anaiytes that fluoresce or are amenable to derivatization with a fluorophore.
  • Microscale CE systems are described generally in, among others, U.S. Patents No. 5,904,824, 6,068,752 and 6,103,199.
  • Electrochemical detection is used in a wide variety of areas. Such detection offers remarkable sensitivity (comparable to that of fluorescence), tunable selectivity, and low-volume requirements. Electrochemical detection is generally described in J. Wang, Analytical Electrochemistry. 2 nd Ed., Wiley- VHC, New York, 2000. Electrochemical detection has proven to be extremely useful for conventional CE systems based on fused-silica capillaries, but has rarely been used for planar micromachined CE chips. The major challenges for such integration are similar to those of conventional CE systems, namely isolation of the working electrode from the high separation voltage and its proper alignment with the capillary.
  • Microscale fluidic devices coupled with electrochemical detection means are applicable to a wide variety of environmental, research, industrial and medical applications, among others. For example, such devices could be used in operating rooms, emergency departments, intensive care units, ambulances, clinics and the like for rapidly and reliably monitoring a wide range of anaiytes. While CE is the primary electrically driven separation modality used in microfluidic applications, other separation modalities have been described for microscale fluidic devices, including pump and other mechanical transport devices.
  • This invention provides an apparatus for conducting a microfluidic process and analysis, which apparatus includes a first substrate, at least one elongated separation channel in the first substrate, the separation channel having an inlet end and an outlet end, a fluidic transport for transport of fluids through the separation channel, a second substrate and at least one thick-film electrode on the second substrate, the thick-film electrode being in fluidic connection with the outlet end of the separation channel.
  • the fluidic transport can be a conductive system in fluidic connection with each end of the separation channel for application of a separation voltage, which conductive system can include electrodes.
  • the apparatus can also include a high-voltage power supply for application of voltage to the conductive system.
  • the fluidic transport can include electrokinetic fluid transport, and may also include other forms of fluidic transport, such as electrical, mechanical, centrifugal, magnetic, pneumatic, pressure-activated, or vacuum-activated fluid transport.
  • the first substrate of the apparatus can include a fused-silica, silica-based, polymer, plastic or elastomer material, and the second substrate can include a ceramic, polymeric or plastic material.
  • the apparatus can include at least one reference electrode in fluidic connection with the thick- film electrode and also an electrical contact to the thick-film electrode.
  • the thick-film electrode may be a screen-printed electrode.
  • the apparatus can include an analyte analysis system in electrical contact with the electrical contact to the thick-film electrode.
  • the apparatus includes an analyte analysis system for analyzing an analyte at the thick-film electrode.
  • the analyte analysis system can o be an amperometric detection system in one embodiment, and may be either a fixed potential or potential-step amperometric detection system.
  • the analyte analysis system can also include a stripping potentiometry system or a voltammetric detection system.
  • the separation channel in the apparatus can have an average bore diameter of from about 1 ⁇ m to about 300 ⁇ m, and preferably from about 20 ⁇ m to about 120 ⁇ m.
  • the separation channel can also include separation media within the channel.
  • the thick-film electrode has a thickness of from about 1 ⁇ m to about 100 ⁇ m, and preferably between about 8 ⁇ m and 30 ⁇ m.
  • the first substrate that includes at least one elongated separation channel is detachable from the second substrate that includes at least one thick-film electrode.
  • the first substrate can be affixed to the second substrate such that the distance between the thick-film electrode and the outlet end of the separation channel is fixed.
  • the distance between the thick-film electrode and the outlet end of the separation channel is from about 1 ⁇ m to about 500 ⁇ m, and preferably between about 50 ⁇ m and about 100 ⁇ m.
  • the thick-film electrode can be a carbon ink electrode, and can also include other constituents.
  • the thick-film electrode can include a metal conducting coating, and can generally include metals, inorganic dopants, organic dopants, nucleic acids, catalytic surface modifiers, enzymatic surface modifiers or permselective film coatings.
  • the apparatus can also include one or more buffer cavities and sample cavities in fluidic connection with the inlet end of the separation channel.
  • One or more reaction cavity in fluidic connection with the inlet end of the separation channel can also be provided.
  • the apparatus can include a plurality of separation channels with the inlet ends thereof in fluidic connection with the cavity. There can also be at least one cavity in fluidic connection with the outlet end of the separation channel.
  • the apparatus can include a plurality of separation channels and a plurality of thick-film electrodes.
  • both the first substrate and the second substrate are substantially planar, and the second substrate is at an angle to the first substrate.
  • the second substrate can be perpendicular to the first substrate.
  • the first substrate and the second substrate can be substantially planar and parallel to each other.
  • the second substrate can form a seal for at least a portion of the separation channel of the first substrate.
  • the invention also includes a method for detecting an analyte, in which are included the steps of introducing the analyte in the inlet end of a microfluidic channel having an inlet end and an outlet end; transporting the analyte in a fluid solution through the microfluidic channel to the outlet end; contacting the solution containing the analyte with a thick-film electrode in fluidic connection with the outlet end of the microfluidic channel; providing electrical contact to the thick-film electrode; and analyzing the analyte at the thick-film electrode by electrochemical detection.
  • This method can include the additional step of providing electrical contact to at least one counter electrode in fluidic contact with the thick-film electrode, and also the optional steps of providing at least one reactant for the analyte and mixing the at least one reactant and the analyte prior to introducing the analyte in the inlet end of the microfluidic channel.
  • the microfluidic channel can include a microfluidic separation channel.
  • Transporting the analyte in a fluid solution through the microfluidic channel is by electrokinetic fluid transport.
  • the electrokinetic fluid transport can be by capillary electrophoresis.
  • the step of transporting the analyte may be by electrical, mechanical, centrifugal, magnetic, pneumatic, pressure-activated, or vacuum-activated fluid transport methods.
  • Analyzing the analyte at the thick-film electrode by electrochemical detection can include amperometric detection, including fixed potential and potential-step amperometric detection. Analyzing can also include stripping potentiometry and voltammetric detection.
  • the distance between the thick-film electrode in fluidic connection with the outlet end of the microfluidic channel and the microfluidic channel can be fixed, and is preferably a distance of from about 1 ⁇ m to about 500 ⁇ m, and preferably between about 50 ⁇ m and about 100 ⁇ m.
  • the thick-film electrode can be a carbon ink electrode, and can optionally include a metal conducting coating, and in general can include metals, inorganic dopants, organic dopants, nucleic acids, catalytic surface modifiers, enzymatic surface modifiers, or permselective film coatings.
  • the fluid solution of the method can be a buffer solution. Any of a variety of reactants, if employed, may be used, including enzymes and derivatizing agents.
  • the analyte can be a nitroaromatic compound, catecholamine, hydrazine compound, phenolic compound, enzyme-specific compound, amino acid, nucleic acid, metal ion or anion.
  • the analyte may be DNA, scDNA, ssDNA, dsDNA, RNA or tRNA.
  • a primary object of the present invention is to provide a method and apparatus to combine microfluidic separation with the ease, cost-advantages and simplicity of thick-film electrochemical detection.
  • Another object of the present invention is to provide a method and apparatus for separation and identification of a wide range of analytes using microfluidic separation and thick-film electrochemical detection.
  • Another object of the present invention is to provide a method and apparatus for an integrated, on-chip combination reaction, separation and electrochemical detection microsystem.
  • Another object of the present invention is to provide an apparatus wherein the thick-film electrochemical detection component may readily be detached from the microfluidic reaction and separation component and replaced.
  • a primary advantage of the present invention is the ease of use and cost advantage resulting from use of thick-film electrochemical detection combination with microfluidic devices, including microfluidic reaction and separation.
  • Another advantage of the present invention is that the thick-film electrode may be fabricated by screen printing.
  • FIG. 1a to 1d schematically illustrates an embodiment of an apparatus in accordance with this invention
  • FIG. 2 schematically depicts an alternative configuration of the separation and reaction component for use with derivatized reactions in accordance with this invention
  • FIG. 3 schematically depicts an alternative configuration of the separation component in accordance with this invention.
  • FIG. 4 depicts an alternative configuration of the separation and reaction component for use in bioassays in accordance with this invention
  • FIG. 5 is a plot of the influence of different carbon inks for the screen-printed carbon electrode on detection of different analytes
  • FIG. 6 is a plot on the influence of separation voltage on detection of different analytes
  • FIG. 7 is a plot on the influence of the distance between the channel outlet and the screen- printed working electrode upon the response at two different separation voltages
  • FIG. 8 is a hydrodynamic voltammogram of two different analytes
  • FIG. 9 is an electropherogram for different concentrations of analytes
  • FIG. 10 is an electropherogram for multiple different analytes
  • FIG. 11 is an electropherogram for different analytes obtained with a bare and palladium- modified screen-printed working electrode;
  • FIG. 12 is a hydrodynamic voltammogram of two different analytes;
  • FIG. 13 is a plot of the influence of the separation voltage on the response at different separation voltages, with an insert showing the effect of separation potential on the resolution and number of apparent theoretical plates for hydrazine;
  • FIG. 14 is an electropherogram for different concentrations of analytes, with an insert showing resulting calibration plots over a specified concentration range;
  • FIG. 15 is a plot of the separation and detection of phenol and six chlorophenols
  • FIG. 16 is a plot of the separation and detection of different analytes
  • FIG. 17 is a hydrodynamic voltammogram of three different analytes
  • FIG. 18 is a plot of the influence of separation voltage on the response for an analyte at different separation voltages, with an insert showing the effect of separation voltage on the number of apparent theoretical plates for one analyte;
  • FIG. 19 is a plot of calibration data, including electropherograms for mixtures containing increasing levels of analytes and an insert showing the resulting calibration plots;
  • FIG. 20 is an electropherogram for river water samples before and after the addition of phenolic compounds
  • FIG. 21 is a schematic diagram depicting enzymatic and separation processes along a separation channel
  • FIG. 22 is an electropherogram for glucose and glucose solutions containing increasing levels of ascorbic acid and uric acid;
  • FIG. 23 is a plot of portions of electropherograms showing measurements of glucose and acetaminophen in the presence and absence of glucose oxidase;
  • FIG. 24 is a plot showing the effect of separation voltage on glucose and other analytes
  • FIG. 25 is a plot of the influence of glucose oxidase concentration on the response to a fixed level of glucose
  • FIG. 26 is a plot of the reproducibility of the current response for glucose and other analytes
  • FIG. 27 is a calibration plot for glucose and other analytes.
  • FIG. 28 is an electropherogram for specified amino acids
  • FIG. 29 is a hydrodynamic voltammogram for specified amino acids
  • FIG. 30 is a plot of the influence of separation voltage on the response with specified amino acids
  • FIG. 31 is an electropherogram for a sample with eight amino acids at altered separation voltages
  • FIG. 32 is a plot of the reactant concentration on the response for a sample mixture of specified amino acids
  • FIG. 33 is a plot of the sample and reactant mixing ratio on the response for specified amino acids;
  • FIG. 34 schematically depicts a microsystem in accordance with this invention with parallel separation and detection components;
  • FIG. 35 schematically depicts a multi-channel microsystem in accordance with this invention.
  • microfluidic separation component may be any means or method of microfluidic separation. In general, this component will consist of at least one channel or fluid conduit, and generally two or more intersecting channels or fluid conduits, and a means for pumping or movement of fluid through one or more channels or fluid conduits. In a preferred embodiment, electoosmotic flow is used to provide movement fluid through microchannels in the microfluidic separation component.
  • electrophoresis and specifically capillary electrophoresis (CE), which includes a variety of forms of separation electrophoresis, including but not limited to capillary zone electrophoresis, capillary gel electrophoresis, capillary isoelectric focusing, capillary isotachophoresis, micellar electrokinetic chromatography and the like.
  • CE capillary electrophoresis
  • all modes and methods of electrokinetic movement of fluids will incorporate one or more electrodes, and generally an electrode at or near to the end of each channel or fluid conduit, or in reservoirs or other areas to which such ends of such channels or fluid conduits are in fluidic communication.
  • electrical potential By application of electrical potential, fluid transfer may be initiated, movement flow rates regulated, transfer from one channel or fluid conduit to an intersecting channel or fluid conduit controlled and the like.
  • mechanical or other pressure-driven flow devices may be used, including external pumps, microfabricated pumps and the like. In the case of microfabricated pumps, such components may form a part of the microfluidic separation component.
  • the motive force employed in driving the fluids may be electrical, mechanical, centrifugal, magnetic, pneumatic, pressure-activated or any other means known in the art.
  • the pumping may be positive, resulting in a pumping pressure, or may be negative, resulting in a vacuum draw.
  • the channels or fluid conduits which may function as microcapillaries, may be of any desired cross-sectional shape, and may be of any longitudinal configuration.
  • the cross- sectional shape may be rectangular, square, circular, half-circular, ellipsoidal, or any other geometric shape, regular or irregular.
  • the cross-section is constant over the longitudinal dimension, or constant within limits of standard manufacturing procedures, so that the volume per given unit length of the channel or fluid conduit is constant, again within limits of standard manufacturing procedures.
  • the dimensions of the cross-sectional shape (the height, width or any diameter) will generally be at least about 1 ⁇ m, usually at least about 10 ⁇ m, and is usually no more than about 500 ⁇ m, and preferably no more than about 100 ⁇ m.
  • the equivalent inside bore diameter is from about 1 to about 300 ⁇ m, and is typically from about 20 to 120 ⁇ m.
  • the cross-section is half-circular, with a maximum depth of about 20 ⁇ m and a width, at the top, of about 50 ⁇ m.
  • the longitudinal configuration may be any configuration that may be described.
  • the channel or fluid conduit may be straight, curved, spiral, serpentine or the like.
  • the required length of the channel or fluid conduit is generally related to the separation technique, media if any, analyte and the like.
  • the length will generally be at least about 1 mm, usually at least about 10 mm, and is usually no more than about 500 mm, and preferably no more than about 100 mm.
  • the effective length of the primary separation channel or fluid conduit is about 72 mm.
  • the channels or fluid conduits are generally a part of a planar substrate.
  • Such channels or fluid conduits may be made by any means known in the art, including microphotolithographic techniques, chemical etching, laser cutting, molding, embossing, drilling, mechanical cutting, machining or scoring, grooving or the like.
  • the planar substrate is conventionally substantially flat, or has at least one substantially flat surface into which the channels or fluid conduits are laid. However, it is also possible and contemplated that the surface of the planar substrate into which the channels or fluid conduits are laid may be curved or otherwise other than flat.
  • the planar substrate may be made of any material which may be employed in conjunction with the analyte, the buffer or other fluids, and the motive force employed for pumping or movement of fluid through one or more channels or fluid conduits of the microfluidic separation component. Because the method of detection is by thick-film electrochemical detection, there is no need for the planar substrate to transmit light, permit fluorescent observation or the like required by other detection modalities, such as laser fluorescence.
  • the planar substrate, or a portion thereof wherein one or more channels or fluid conduits are located may be constructed of f used-silica, glass, other silica-based substrates, gallium-based substrates, plastics, polymeric materials, elastomeric materials, and the like. In one embodiment, a solid or semi-solid substrate that is compatible with microfabrication techniques, such as photolithography, is employed.
  • the inside surface of one or channels or fluid conduits is coated with a material, which material may be used to provide strength, assist in regulating the motive force employed for pumping or movement of fluid, provide compatibility with buffers or analytes, or the like.
  • a material which material may be used to provide strength, assist in regulating the motive force employed for pumping or movement of fluid, provide compatibility with buffers or analytes, or the like.
  • Such material may be any art conventional material, including polymeric materials, and may thus include silicon-based coatings, polyacrylamides, polyvinyls, polyethylenes, polyesters, polyethers, TeflonTM (DuPont), NationalTM (DuPont), and the like.
  • the material may be applied by any known coating method, including plasma deposition, sputtering, electrochemical attraction, plating, immersion, spraying, or the like.
  • the interior surface of the channel or fluid conduit may be altered, such as by application of a coating or mask, such that portions thereof are relatively hydrophobic and other portions thereof are relatively hydrophilic.
  • each channel or fluid conduit there is located at least one of an inlet port, channel outlet, reservoir, cavity, chamber, well or the like.
  • Such components may be in series, so that, for example, an inlet port is in fluid connection with a reservoir or other cavity, which in turn is in fluid connection with one end of the channel or fluid conduit.
  • the reservoir, cavity or similar structure may serve any of a number of purposes, including as an incubation chamber, reagent reservoir, running buffer reservoir, sample reservoir, separation chamber, reaction chamber, detection chamber in fluid communication with the thick-film electrochemical detection component, injection waste reservoir, enrichment chamber or the like.
  • Reservoirs, cavities and the like may be of any size and volume consonant with the intended purpose, and may include cavities or wells, enlarged portions of the channel, or the like.
  • the channel outlet is in connection with a cavity, such as a detection chamber in fluid communication with the thick-film electrochemical detection component.
  • an inlet port is in fluid communication with a cavity, such as an incubation chamber, reagent reservoir, running buffer reservoir, sample reservoir, or reaction chamber, which in turn is in fluid communication with the channel or fluid conduit.
  • two or more channels or fluid conduits may be in fluid communication with one cavity, such as an incubation chamber, reagent reservoir, running buffer reservoir, sample reservoir, separation chamber or reaction chamber, and further is contemplated that the motive force employed for pumping or movement of fluid may selectively cause movement of fluid through one or more of the channels or fluid conduits.
  • a selective electrokinetic system is employed, whereby movement of fluid may be effected to one or more selected channels or fluid conduits in fluid communication with a cavity, including an intersecting channel or fluid conduit, such as by selective application of potential to selected electrodes located at or near ends of or along the length of some or all of the channels or fluid conduits.
  • any of a wide variety of either pre-separation or post-separation derivatization reactions may be conducted.
  • Such cavities, chambers or reservoirs may optionally be heated, such as by heating resistors, to optimize the derivatization method employed.
  • electrochemical detection may be employed with selected non-electroactive analytes.
  • Such channels or fluid conduits may intersect other channels or fluid conduits, which intersection may be at any angle. It is possible and contemplated that more than two such channels or fluid conduits may intersect at a given point. It is also possible and contemplated that a multiplicity of channels or fluid conduits, such as three or more, meet at a given point, and are thereby in fluid connection one with the other, without any given channel or fluid conduit continuing past such point, as in a star-burst configuration. The intersection may optionally, but need not, form a cavity, well or reservoir.
  • fluids may enter through any one or more of the intersecting channels or fluid conduits, and may be caused to exit or outlet through any other one or more of the intersecting channels or fluid conduits.
  • the intersection acts as a valve, which may be a selectable and changeable valve, such that the operator may select one or more inlet channels or fluid conduits, and one or more outlet channels or fluid conduits.
  • a selective electrokinetic system is employed, whereby movement of fluid may be effected to one or more selected inlet channels or fluid conduits in fluid communication with one or more selected intersecting outlet channels or fluid conduits, such as by selective application of potential to selected electrodes located at or near ends of or along the length of some or all of the channels or fluid conduits.
  • the planar substrate may form a part of an integrated on-chip combination reaction, separation and detection microsystem.
  • the integrated on-chip microsystem, including the planar substrate may further include electrodes, printed circuit connectors and the like, particularly for the application of electrokinetic flow, CE and the like.
  • Such electrodes may conventionally be platinum wires, but may be any convenient type capable of applying an appropriate electric field to the fluid or other medium in the channel or fluid conduit with which they are associated.
  • Such electrodes may thus be made of any suitable conductive material, and may be applied by any means known in the art, including sputtering, plating, painting, and the like, as well as use of wires, strips, rods or the like as electrodes.
  • At least one electrokinetic flow electrode is placed at or near each end of any given channel or fluid conduit, though it is possible that a single electrode, such as an electrode placed at an intersection of two or more channels or fluid conduits, or in a reservoir or cavity with which two or more channels or fluid conduits are in fluid communication, may serve as a terminus electrode for more than one channel or fluid conduit. It is also possible and contemplated that a multiplicity of electrodes, such as more than two, are placed along the length of the channel or fluid conduit, such that, for example, the rate of flow of fluid through the channel or fluid conduit may be altered along the length of such channel or fluid conduit. Connections to such electrodes may form a part of the integrated on-chip microsystem, and may terminate in one or more plugs, connector strips, pins, pin sets, chip holders and connectors, or the like.
  • Such electrokinetic electrodes are connected to a high-voltage power supply, and preferably a power supply with multiple independent and selectable voltage terminals for connection to each electrode.
  • Any effective driving voltage may be employed; in general, the driving voltage for both movement of fluid and switching between modes, reservoirs, channels or the like is between about 0 and about +30,000 volts (V) and preferably between about 0 and about +4000 V.
  • the power supply may be integrated into a computer-based system, and may further be integrated into a computer- based system which also controls amperometric detection using the thick-film electrochemical detection component, which system may be programmable, include appropriate feed-back and control systems, record data, produce output records of data, and the like.
  • the integrated on-chip combination reaction, separation and detection microsystem may include a multiplicity of CE separation channels or fluid conduits, which may permit simultaneous detection of different analytes in a common sample, detection of the same analyte in multiple different samples, or any combination thereof.
  • a sample inlet port may be connected to one or more sample reservoirs, with any number of separation channels or fluid conduits in fluid connection with such reservoir or reservoirs.
  • the separation channels or fluid conduits are arranged in a star-burst configuration, with a multiplicity of separation channels or fluid conduits emanating from and in fluid connection with a common central sample reservoir, which in turn is in fluid connection with an inlet port.
  • the multiplicity of separation channels or fluid conduits are in fluid communication with one or more reagent reservoirs, running buffer reservoirs and the like, such that different reagents, buffers or the like may selected for different separation channels or fluid conduits.
  • the separation channels or fluid conduits may include therein a separation matrix element, such as a gel, membrane, polymeric material, polymeric particles or the like, including those materials and elements used in conventional separation techniques, such as chromatography, electrophoresis, and other analytical separation methods and techniques.
  • a separation matrix element such as a gel, membrane, polymeric material, polymeric particles or the like, including those materials and elements used in conventional separation techniques, such as chromatography, electrophoresis, and other analytical separation methods and techniques.
  • Use of such sieving or separation methods may reduce the length of the separation channel or fluid conduit required to obtain the desired degree of separation.
  • buffers Any of a wide variety of buffers, including conventional buffers, may be employed in the integrated on-chip combination reaction, separation and detection microsystem of this invention.
  • the selection of buffers is largely dependent on the analyte, the specific separation technique employed and the specific detection system employed.
  • MES, borate, SDS, PBS, borate/phosphate, phosphate, and the like may be employed, as well as buffers such as HEPES, MOPS, MES, Tricine, Tris, acetate, citrate and the like.
  • the buffers may include additives such as alcohols, surfactants, detergents and the like.
  • Exemplary buffer systems include: a) 25 mM 2-(4- morpholino)ethanesulfonic acid hydrate at pH 6.5; b) 15 mM sodium borate with 25 mM sodium dodecyl sulfate at pH 8.7; c) 10 mM phosphate at pH 7.3 with 1 mM potassium chloride; d) mixed 10mM each borate and phosphate buffer at pH 8.0; e) 10 mM borate buffer at pH 10.5; f) 10 mM phosphate buffer at pH 7.4; and g) 20 mM sodium borate with 30 mM sodium dodecyl sulfate at pH 9.4.
  • Such buffers may optionally be filtered, such as by use of a 0.45 ⁇ m filter, prior to use.
  • Any of a wide variety of reactants may be employed, either as components of the buffer, or as separate reactants introduced into the system through an inlet port, and optionally placed into a reaction chamber.
  • Typical reactants include any of a wide variety of enzymes, such as glucose oxidase enzyme. There are over 200 dehydrogenase redox enzymes and over 100 oxidase enzymes known to the art which generate electrochemically detectable products. It is also possible and contemplated that multiple simultaneous oxidase- and dehydogenase-based reactions may be conducted.
  • a reactant there may be multiple cavities, wells, chambers or reservoirs, such as a buffer reservoir, which contains only buffer, a reactant reservoir, which contains a mixture of a reactant with a buffer, and the like.
  • a buffer reservoir which contains only buffer
  • a reactant reservoir which contains a mixture of a reactant with a buffer
  • such reactants also include those required for the derivatization reaction.
  • such reactants may include o-phthalaldehyde, 2-mercaptoethanol, and the like, together with other components such as sodium borate, methyl alcohol and the like.
  • a derivatization reaction chamber may be provided.
  • the separation channels or fluid conduits are in fluid connection with the thick-film electrochemical detector component forming a part of the integrated on-chip combination reaction, separation and detection microsystem.
  • a channel outlet from the separation channel or fluid conduit is in fluid connection with the surface of a thick-film working electrode, such as a screen- printed carbon-based working electrode.
  • the distance between the channel outlet and the electrode surface may be modified as required for the analyte, separation technique and electrochemical detection technique, but in general such distance will be between about 1 ⁇ m and about 500 ⁇ m, and preferably between about 50 ⁇ m and 100 ⁇ m.
  • the distance may be controller by a thin-layer spacer of suitable thickness.
  • the thick-film electrochemical detector component may be detachable from the reaction and separation components of the integrated on-chip combination reaction, separation and detection microsystem.
  • the thick-film electrochemical detector component may be affixed to the remaining components of the microsystem by a snap, friction fitting, set screw, slide fastener, clip, or the like, and may be constructed such that the thick-film electrochemical detector component may be rapidly replaced by the user, such as in less than one minute, and preferably in less than about ten seconds. Such replacement may be performed to replace a fouled, passivated or damaged thick-film electrochemical detector component, to substitute a thick-film electrochemical detector with different working electrode components, and the like.
  • the thick-film electrochemical detector component is perpendicular to the separation channel or fluid conduit.
  • the channel outlet terminates opposite of, and within the specified distance from, the surface of the working electrode forming a part of the thick-film electrochemical detector component.
  • the planar substrate containing the separation channel or fluid conduit is parallel to and in communication with the thick-film electrochemical detector component.
  • the thick-film electrochemical detector component may form a lower plate, with the planar substrate containing the separation channel or fluid conduit forming an upper plate, such that the outlet channel is within a specified distance from the surface of the working electrode.
  • the planar substrate may be plastic or another polymeric material, and have photolithographed, cut, etched or otherwise placed thereon the channels, fluid conduits, cavities and the like, with the lower plate forming a seal or bottom surface for such channels, fluid conduits, cavities and the like.
  • the thick-film electrochemical detector may be made on a ceramic wafer, or optionally on any other material that is suitably inert and non-conductive, such as preferably a plastic substrate.
  • the detection reservoir which is in fluid connection with the outlet channel, may include therein one or more electrodes, such as one or more platinum wires and an Ag/AgCI wire. One or more of the platinum wires may serve as a contact for the high-voltage power supply, serving as an electrokinetic flow electrode.
  • An additional platinum wire and the Ag/AgCI wire may serve as counter and reference electrodes, respectively, for detection. Detection may be by amperometric, voltammetric or potential detection.
  • the Ag/AgCI wire may be prepared by electrochemical oxidization of a silver wire in 0.10 M hydrochloric acid.
  • other electrodes known in the art, may serve as the counter and reference electrodes. It is also possible that a two electrode system is used, such as for amperometric detection, consisting of the screen-printed or otherwise fabricated thick-film working electrode and a reference electrode.
  • a 100 x 100 x 0.64 mm alumina ceramic plate is used for the thick-film electrochemical detector.
  • the screen-printed working electrode is printed with a printer, such as a semi-automatic printer (Model TF 100, MPM, Franklin, MA), with printing through patterned stencils (100 ⁇ m thick, Specialty Photo-Etch, Inc., TX) onto the alumina ceramic plate.
  • a printer such as a semi-automatic printer (Model TF 100, MPM, Franklin, MA)
  • stencils 100 ⁇ m thick, Specialty Photo-Etch, Inc., TX
  • Each plate consists of 30 strips (33.3 x 10.0 x 0.64 mm) with each strip being defined by a laser pre/semi cut.
  • a carbon ink working-electrode layer (Acheson ink Electrodag 440B, Acheson Colloids, Ontaria, CA) of 0.3 x 8.0 mm is first printed on each of the strips of the alumina ceramic plate and is cured at about 100° C for about 30 minutes.
  • a silver ink (Ercon R-421(DRE-63)) contact layer of 1.5 x 21.0 mm, partially overlapping the carbon layer, is printed and cured at about 100° C for about 30 minutes.
  • An insulating ink (Ercon R-488CI-G1 Insulator Green) layer is subsequently printed to cover the carbon- silver junction and to define the working electrode area, 0.30 x 2.5 mm, on one end, and to expose the contact area on the other side.
  • the strips are then cured at about 100° C for about 120 minutes.
  • the cured layers of carbon, silver, and insulator have a thickness of approximately 10, 28 and 70 ⁇ m, respectively.
  • the carbon ink working electrode active area may be subsequently modified.
  • a palladium-modified screen-printed electrode is prepared by scanning or cycling the potential between about +0.6 V and -0.6 V, against the Ag/AgCI reference electrode, for 60 cycles in a 0.5 M HCl solution containing 1000 ppm Pd(VI).
  • the carbon working electrode area is coated with gold by applying a pulse waveform, again against the Ag/AgCI reference electrode, in a solution containing 300 ppm Au(lll), 0.1 M NaCl and 1.5% (w/v) HCl.
  • the surface of the working electrode may similarly be modified by other means known in the art, including coating with other metals, use of various dopants, use of catalytic or enzymatic surface modifiers, permselective film coatings, or the like.
  • the working electrodes via the silver ink contact layers, and the platinum wires and the Ag/AgCI wires serving as counter and reference electrodes, are connected, through one or more plugs, connector strips, pins, pin sets, connectors, or the like, to a detection device, such as an amperometric detection device.
  • a detection device such as an amperometric detection device.
  • a device such as an Electrochemcial Analyzer 621 (CH Instruments), connected to a computer, is employed.
  • the amperometric detection device should have such inputs as are required for the number of working electrodes to be detected, and should work over a suitable scanning voltage range, from a potential of between about +1.0 and -1.0 V against the reference electrode, and cycling in a variety of wave forms over a range of pulse widths.
  • the amperometric detection device may be integrated into a computer-based system, and may further be integrated into a computer-based system which also controls the high- voltage power supply, which system may be programmable, include appropriate feed-back and control systems, record data, produce output records of data, and the like. It is possible and contemplated that the entire integrated on-chip combination reaction, separation and detection microsystem, including the microfluidic separation component, the thick-film electrochemical detection component, the high-voltage power supply, the amperometric detection device, data recording elements and other components parts may be made into a single device, with a removable and replaceable thick-film electrochemical detector component, and optionally a removable and replaceable microfluidic separation component. Such single device may be a portable device, and may further be a hand-held device. Such device may be connected to data acquisition devices by any means known in the art, including wires, infrared, radio or the like.
  • Amperometric detection may be by either fixed-potential and potential-step amperometric detection. However, it is also possible and contemplated that other electrochemical detection modes may be employed, depending on the specific analyte, microfluidic or separation system, reactants if any, detector components and the like, as are taught generally in J. Wang, Analytical Electrochemistry. 2 nd Ed., Wiley- VHC, New York, 2000.
  • electrochemical detection may be employed, including potential-sweep or scanning potential voltammetric modes, cyclic voltammetry, pulse voltammetry, including normal-pulse, differential-pulse, square-wave and staircase voltammetry, potentiometric stripping analysis, adsorptive stripping voltammetry and potentiometry, and the like.
  • the channels may be rinsed with a suitable cleaning solution, such as sodium hydroxide, hydrochloric acid, deionized water or the like. Electrokinetic transport may be used for cleaning the channels.
  • a suitable cleaning solution such as sodium hydroxide, hydrochloric acid, deionized water or the like. Electrokinetic transport may be used for cleaning the channels.
  • the appropriate reservoirs are filled, or partially filed, with the appropriate buffer, analyte or reactants. In one embodiment, from about 10 ⁇ L to about 250 ⁇ L of buffer is placed in the buffer reservoir, and from about 10 ⁇ L to about 250 ⁇ L of sample containing the analyte is place in the sample reservoir.
  • about 80 ⁇ L of reactant is placed in a reactant or reagent reservoir
  • two or more buffer reservoirs have about 80 ⁇ L of buffer placed in each
  • Such placement may be by any art conventional means, including use of pipettes, micropipettes, pipette tips and the like.
  • the injection channel may be filled with sample solution by application of about +1500 V for about 30 seconds to the sample reservoir with the detection reservoir grounded and the buffer reservoir floating, it being understood that the applied voltage and time may be modified as required for the specific device and conditions.
  • a voltage of about +1500 V for about 60 seconds may be applied to both, with the detection reservoir grounded and other reservoirs floating, such that the reaction chamber is filled at a constant mixing ratio.
  • sample and reactant mixing ratios may be applied by independently altering the current flows to the reactant and sample reservoirs, such as through use of different resistors.
  • a sample plug may be loaded into the separation channel, such as by application of +1500 V to the sample reservoir, injection channel, reaction chamber, combination of the sample and reaction reservoirs or the like, for a suitable time, such as about three seconds.
  • An injection time of three seconds, in certain systems, corresponds to an injected volume of about 2 nL.
  • the injection time and voltage may be altered as required to produce the desired injection volume.
  • Separation is performed by applying an appropriate voltage, such as from about +1000 to about +3000, to the running-buffer reservoir with the detection reservoir ground and other reservoirs floating. Voltage is applied for so long as is required to obtain desired electrochemical data.
  • Electrochemical detection is by amperometric detection over a suitable voltage range, from a potential of between about +1.0 and -1.0 V against the reference electrode, with an appropriate time resolution, such as about 0.1 seconds.
  • Separation component 10 may be a glass microchip, as described above, or any other suitable material, on which is made a separation channel 20, which may be made by microphotolithographic techniques. Intersecting channel 20 is injection channel 24; the separation channel 20 continues along portion 22 from the intersection with injection channel 24. Separation channel 20 terminates in channel outlet 25.
  • Reservoir 30 is a sample reservoir, accessed by pipette injection port 36; Reservoir 32 is an additional reservoir, which in some embodiments is not employed and in others is used as the reactant reservoir; reservoir 32 is accessed by pipette injection port 46, which in embodiments in which reservoir 32 is not employed is blocked.
  • Reservoir 34 is a buffer reservoir or running buffer reservoir, accessed by pipette injection port 38. As shown in FIB. 1b, the reservoirs 30, 32 and 34 actually form a part of base 62, which may be made of Plexiglass or any other plastic or formabie or machinable material; base 62 is sealed to separation microchip 10, such as by silicone grease or any other form of sealant.
  • a recessed groove 68 is provided to secure separation microchip 10 such that the reservoirs 30, 32 and 34 are in proper alignment with channels 22 and 24.
  • Electrodes 70 are in the base of each of reservoirs 30, 32 and 34, and may be a platinum wire, serving as a contacting for the high-voltage power supply. Each of electrodes 70 are connected to connector 72, to which electrical contact is made.
  • a detection component holder 80 which holder 80 may form a part of base 62, or may be separate as depicted. Holder 80 is similarly fabricated from Plexiglass or any other plastic or formable or machinable material. Holder 80 includes detection reservoir 88 with slot 89 for receiving detection component 50.
  • a recessed groove 86 is provided to secure separation microchip 10.
  • a high-voltage power electrode 90 such as a platinum wire
  • counter electrode 94 connected to connector 98
  • reference electrode 96 connected to connector 100.
  • Counter electrode 94 may be a platinum wire, or any other suitable counter electrode material for use in amperometric detection.
  • Reference electrode 96 may be an Ag/AgCI wire, such as prepared by electrochemical oxidation of a silver wire in 0.10 M hydrochloric acid, or any other suitable reference electrode material for use in amperometric detection.
  • threaded cylinder 82 with which plastic screw 84 is threadably engaged, and tightly secures detection component 50 in slot 89.
  • detection component 50 on which is screen printed working electrode 104, which may be a carbon ink based strip, approximately 0.3 x 8.0 mm, and 10 ⁇ m thick.
  • a silver ink contact layer 102 is printed over a portion of the working electrode 104, the silver ink contact layer 102 being approximately 1.5 x 21.0 mm, and approximately 28 ⁇ m thick.
  • An insulating ink layer 106 is printed over the working electrode 104 and silver ink contact layer 102, forming and defining a working electrode area of approximately 0.3 x 2.5 mm, and leaving the end of silver ink contact layer 102 available for connecting to an amperometric detection device.
  • the insulator has a thickness of 70 ⁇ m.
  • spacers 108 and 110 which control the distance between the working electrode 104 and the channel outlet 24; such spacers 108 and 110 have a nominal thickness of 60 ⁇ m and may be made of tape or another suitable material.
  • FIG. 2 id a schematic of an integrated reactor and separation microchip with electrochemical thick-film detection.
  • S is the sample reservoir
  • R is the reagent reservoir
  • RB is the running buffer reservoir
  • B is the buffer reservoir
  • RC is the reaction channel
  • D is the detector, a thick- film working electrode. Electrodes for electrokinetic movement of fluids, or other fluid transfer components, are not shown.
  • the reaction chamber 200 ⁇ m wide and 3.6 mm long, is connected through 50 ⁇ m wide channels to the reagent and sample reservoirs at one side, and to a four-way injection cross at the other side.
  • the separation channel is 74 mm long and 50 ⁇ m wide.
  • FIG. 3 is a schematic of the device of FIG. 1.
  • FIG. 3 is a schematic of the device of FIG. 1.
  • GOx glucose oxidase
  • FIG. 34 is an embodiment in which the separation component 120 is parallel to the detection component 140.
  • Separation component 120 includes reservoirs 122, 124 and 126, which be sample, buffer or reactant reservoirs, with reservoirs 122 and 126 connected by channel 128.
  • the channel 130 is a separation channel, terminating in outlet 132.
  • Separation component 120 is in contact with, and optionally detachable from, detection component 140, such that the outlet 142 is between about 1 ⁇ m and 500 ⁇ m, and preferably between about 50 ⁇ m and 100 ⁇ m, from the thick- film working electrode 142.
  • An insulating layer 144 covers that portion of the screen-printed working electrode not in fluid contact with outlet 142, with a connector 146 for electrical contact.
  • This embodiment may also include a waste or detector reservoir, electrokinetic electrodes, reference electrodes and other features shown on FIG. 1.
  • FIG. 35 depicts a multi-channel microchip for parallel emzyme-based assays using a single sample. This format also provides for both pre- and post-separation derivatization reactions.
  • the device and methods of this invention may be employed for the detection of any of a wide range of substances. These include nitroaromatic compounds, catecholamines, hydrazine compounds, phenolic compounds, glucose, lactate, amino acids, nucleic acids, including DNA and RNA, metal ions, anions, and a wide range of other compounds, in general, any electroactive analyte or derivitizable non-electroactive analyte may be detected using the device and methods of this invention.
  • Electrophoresis is widely used for analysis of nucleic acids and similar separations methodologies may be included, including use of capillary gel electrophoresis and capillary zone electrophoresis.
  • the methods may be employed for oligunucleutide quality control, quantitative viral load determination, gene expression studies, analysis of DNA-protein interactions, genotyping, DNA sequencing and the like.
  • potentiometric stripping measurements may be made of extremely low levels of DNA or RNA following adsorptive accumulation onto the working electrode surface.
  • Another method of detections involves hybridization recognition at a probe-coated working electrode for sequence-selective biosensing. Both methods are described in more detail in U.S. Patent No. 6,063,259. Scanning potential voltammetric modes are also possible and contemplated for such detection.
  • the device and methods of this invention may be used for any of a wide variety of medical, clinical, research, environmental, industrial or other applications.
  • devices of this invention could be used: a) to determine glucose or other analyte levels in patients; b) to monitor for presence of explosives in airports and other high security areas; c) to monitor for pollutants and contaminants in water, soil or other substrates; d) for in-process quality control in manufacturing or synthesis processes; e) for automated DNA sequencing; f) for research applications; and the like.
  • the device and methods of the invention may be used in any application wherein an analyte must be detected or quantitated.
  • a high-voltage power supply with an adjustable voltage range between 0 and + 4000 V was employed.
  • Glass microchannel separation chips were fabricated at Alberta Microelectronic Corp. (AMC Model MC-BF4-001 , Edmonton, Canada), using standard microphotolithographic technology, including wet chemical etching and thermal bonding techniques, as depicted in FIG. 1a.
  • the resulting glass chip 10 consisted of a glass plate (120 x 87 mm), with a 77 mm long separation channel 20 located between a deliberately blocked and unused reservoir 32 and the channel outlet 24 at the detection reservoir 88, and a 10mm long injection channel 24, located between the sample reservoir and the buffer reservoir.
  • Each channel had a half-circle cross section, with a maximum depth of 20 ⁇ m and a width of 50 ⁇ m at the top. It was constructed such that pipette tips could be inserted into holes in the buffer and sample reservoirs.
  • the glass chip was fixed in a laboratory-built Plexiglass holder, as depicted in FIG. 1b, with silicone grease providing sealing.
  • the holder contained reservoirs for the sample and buffer solutions, a detection reservoir and an unused reservoir.
  • a platinum wire was inserted into each reservoir and served as contacts for the high voltage power supply.
  • An additional platinum wire and an Ag/AgCI wire were inserted into the detection reservoir, serving as the counter and reference electrodes, respectively, for amperometric detection.
  • the Ag/AgCI wire was prepared by electrochemical oxidization of a silver wire in 0.10M hydrochloric acid.
  • the detection reservoir FIG. 1c had a special groove into which the screen-printed electrode strip FIG. 1d, fit exactly, to allow reproducible and stable positioning, perpendicular to the flow direction.
  • the screen-printed electrode strip was further held in place by a plastic screw pressing the strip against the channel outlet.
  • Amperometric detection was performed with an Electrochemical Analyzer 621 (CH Instruments) connected to a Pen
  • Screen-printed electrodes were printed with a semi-automatic printer (Model TF 100, MPM, Franklin, MA).
  • One of three different carbon inks were utilized for fabricating the working electrode, Acheson ink Electrodag 440B (49AB90) (Acheson Colloids, Ontario, CA), Ercon ink G-448(l) (Ercon, Waltham, MA) and a ESL ink RS12113 modified to contain 30% extra carbon (Electro-Science Laboratories Inc., PA).
  • Printing was performed through patterned stencils (100 ⁇ m thick, Specialty Photo-Etch, Inc., Texas) onto 100 x 100 x 0.64 mm alumina ceramic plates.
  • Each plate consisted of 30 strips (33.3 x 10.0 x 0.64 mm) with each strip being defined by a laser pre/semi cut.
  • the total printing procedure consisted of the following steps. A carbon ink working-electrode layer (0.3 x 8.0 mm) was first printed on each of the strips of the ceramic plate and was cured at 100° C for 30 minutes. Then, a silver ink (Ercon R-421 (DRE-68)) contact layer (1.5 x 21.0 mm), partially overlapping the carbon layer, was printed and cured at 100° C for 30 minutes.
  • An insulating ink (Ercon R-488CI-G1 Insulator Green) layer was subsequently printed to cover the carbon-silver junction and to define the working electrode area (0.30 x 2.5 mm) on one end, and to expose the contact area on the other side.
  • the strips were then cured at 100° C for 120 minutes.
  • the cured layers of carbon, silver, and insulator had a thickness of 10, 28 and 70 ⁇ m, respectively.
  • pieces of tape (Scotch, Magic Tape 810) with a thickness of 60 ⁇ m each, were placed as shown in FIG. 1d. The tape served as a spacer, controlling the distance between the strip and the channel outlet.
  • Example 3 Electrophoresis Procedure for Catecholamines and Nitroaromatic Explosives
  • the channels of the CE chip of Example 1 were treated by rinsing with a 1.0 M sodium hydroxide solution for 20 minutes, followed by deionized water for 1 minute, 1.0% hydrochloric acid for 20 minutes, and finally with deionized water for 1 minute.
  • the buffer and sample reservoirs in the chip holder and the corresponding pipette tips on the micro- channel chip were filled with 250 ⁇ l buffer and sample solutions, respectively.
  • the chip was then placed in its holder with the pipette tips pointing downwards into the reservoirs and the detection reservoir was filled with buffer solution. Finally, the high voltage power supply was connected to the reservoirs.
  • +1500 V was applied for 30 seconds to the sample reservoir with the detection reservoir grounded and the buffer reservoir floating. Separations were typically carried out by applying +1500 V to the buffer reservoir with the detection reservoir grounded and the sample reservoir floating.
  • the electrophoresis buffer consisted of MES buffer (25 mM, pH 6.5) for the separation of catecholamines, with injection or sample "loading" performed by applying +1000 V to the sample reservoir for 2 seconds with the detection reservoir grounded and the buffer reservoir floating.
  • the injection was carried out by applying +1500 V to the sample reservoir for 3 seconds, with the detection reservoir grounded and the buffer reservoir floating. Prior to use, all buffer solutions were filtered through a 0.45 ⁇ m filter (Gelman Acrodisc) and sonicated for 20 minutes.
  • Electropherograms were recorded after background stabilization, with a time resolution of 0.1 second, using applied detection potentials (vs. Ag/AgCI) of +0.70 V for catecholamines and -0.70 V for explosives.
  • vs. Ag/AgCI applied detection potentials
  • FIG. 5(a) displays electropherograms for an equimolar (100 ⁇ M) mixture of dopamine (DA) and catechol (CA) using detectors based on the Ercon (A), Acheson (B), and ESL (C) carbon inks of Example 1, and a separation voltage of +1500 V, using the device of Examples 1 and 2 and the methods of Example 3.
  • MES buffer 25 mM, pH 6.5 was used as the electrophoresis buffer, with sample injection at +1000 V for 2 seconds and detection at +0.70 V using a 60 ⁇ m spacing between the electrode surface and the channel outlet.
  • the Ercon and Acheson based working electrodes resulted in well-defined, sharp and resolved peaks, a flat baseline, and favorable signal-to-noise characteristics. No response is observed using the ESL working electrode (C(a)).
  • Anodic activation often used for enhancing the electrochemical reactivity of thick-film detectors, offered a dramatic improvement of the response of the ESL-based detector (C(b)).
  • Such treatment yields no further enhancement of the signals observed with the Ercon and Acheson electrodes (A and B (b)).
  • Ercon- based thick-film detectors were selected for subsequent use as described in Examples 5 and following.
  • FIG. 6 examines the influence of the separation voltage upon the response (using a 60 ⁇ m spacing between the channel outlet and the electrode surface) of the device of Examples 1 and 2, using the methods of Example 3, for detection of 100 ⁇ M dopamine and catechol.
  • the separation efficiency, the current signals, and baseline slope were affected by the separation voltage.
  • Increasing the voltage from +1000 to +4000 V (in 1000 V steps, a-d) dramatically decreased the retention times for both analytes.
  • the largest amperometric signals were observed using the +2000 V separation, while the +4000V separation results in small peaks over a sloping baseline.
  • the separation voltage has a small effect upon the background noise.
  • FIG. 7 depicts the effect of spacing of the distance between the channel outlet and the screen printed working electrode on the response for 100 ⁇ M dopamine and catechol using separation voltages of +1500 (A) and +3000 V (B) with the device of Examples 1 and 2 and the general methods of Example 3.
  • the screen-printed strip was separated from the channel outlet by a distance of (a) 60, (b) 120, (c) 180 and (d) 240 ⁇ m.
  • +1500 V separations the amperometric signal decreased dramatically ( ⁇ 10 fold) upon increasing the spacing between 60 and 240 ⁇ m (a-d, A).
  • the spacing also influenced the separation efficiency, as indicated from the decrease in the number of theoretical plates, from 4400 to 130 (for dopamine) and from 4100 to 490 (for catechol) between 60 and 240 ⁇ m, respectively.
  • Such change in the separation efficiency reflects increased postcapillary diffusional broadening at large channel-electrode distances. Longer channels can be used for improving the separation efficiency.
  • the peak broadening at the larger spacing is coupled to a slight increase in the retention times, from 49 to 55 seconds (for dopamine) and from 88 to 94 seconds (for catechol) between 60 and 240 ⁇ m.
  • FIG. 8 depicts hydrodynamic voltammograms for the oxidation of 100 ⁇ M catechol (a) and 100 ⁇ M epinephrine (b) with the device of Examples 1 and 2 and the general methods of Example 3.
  • the curves were taken stepwise, in conjunction with a 1500 V CE separation, by making 100 mV changes in detection potential. Neither compound displayed any response below +0.40 V. The response rose gradually between +0.50 and +0.90 V, after which it leveled off.
  • the half-wave potentials are +0.66 V (epinephrine) and +0.69 V (catechol).
  • Such drawn out voltammograms reflect the resistance of the printed carbon composite surface.
  • the thick-film electrochemical CE detector displayed well-defined concentration dependence. Electropherograms for sample mixtures containing increasing levels of dopamine and catechol in 2 x 10 '5 M steps are shown in FIG. 9(a-e) using the device of Examples 1 and 2 and the general methods of Example 3.
  • the sample mixtures contained 20 (a), 40(b), 60 (c), 80 (d) and 100 (e) ⁇ M catechol and dopamine. Defined peaks proportional to the analyte concentration were observed for both compounds.
  • the resulting calibration plots were linear with sensitivities of 0.160 and 0.0610 nA/ ⁇ M for dopamine and catechol, respectively (correlation coefficients, 0.998 and 0.989).
  • Example 9 Reproducibility The high sensitivity and speed of the CE/thick-film detector system was found to be highly reproducible. A series of 20 repetitive injections using the device of Examples 1 and 2 and the general methods of Example 3 of a 50 ⁇ M dopamine solution, using the same detector strip, gave a mean value of 7.4 nA and a relative standard deviation of 4.3%. Different detector strips also displayed a good precision. The design of the microsystem permitted rapid 5 - 10 second replacement of the detector strip.
  • FIG. 10 demonstrates the utility of the CE/electrochemical system for analyzing a mixture of common nitroaromatic explosives with the device of Examples 1 and 2 and the general methods of Example 3.
  • the inherent redox activity of nitroaromatic explosives makes them ideal candidates for electrochemical detection.
  • Amperometric detection has been employed previously for measuring nitroaromatic explosives following their conventional CE separations, but not for microscale on-chip analysis.
  • the microchip explosive analysis was performed with a borate buffer (15 mM, pH 8.7) containing 25 mM SDS.
  • 10 shows rapid separation and detection of five explosive compounds, (DNB, 2,4-DNT, 2,6-DNT, 4-NT and TNT, each at 10 mg/L except for 4- NT, which was at 20 mg/L), in a total time of approximately 3 minutes using a separation potential of +1500 V and 60 ⁇ m spacing between the detector and channel outlet.
  • a separation potential +1500 V and 60 ⁇ m spacing between the detector and channel outlet.
  • the thick-film electrochemical detector displayed low background noise and sharp peaks for these 10-20 mg/L concentrations.
  • a chip-based CE/amperometric system for the separation and detection of hydrazine compounds was constructed. Because of the toxicological significance of hydrazine compounds, a reliable method is required for their environmental and industrial monitoring.
  • the screen-printed electrodes were printed with a semiautomatic printer again using Acheson ink Electrodag 440B was used for printing electrode strips as described in Example 2.
  • the palladium-modified screen-printed electrode was prepared by scanning (cycling) the potential between +0.6 and -0.6 V (vs. Ag/AgCI wire) for 60 cycles in a 0.5 M HCl solution containing 1000 ppm Pd(VI).
  • Example 12 Electrophoresis Protocol for Separation and Detection of Hydrazine Compounds An apparatus as in Examples 1 and 11 , with the Palladium-deposited detectors of Example
  • the channels were treated by rinsing with 0.1 M sodium hydroxide and deionized water for 20 and 5 minutes respectively.
  • the buffer and sample reservoirs in the chip holder and the corresponding pipette tips on the micro-channel chip were filled with 200 ⁇ L of buffer and sample solutions, respectively.
  • the chip was then placed in the chip holder with the pipette tips pointing downwards into the reservoirs, while the detection reservoir filled with buffer solution.
  • the high-voltage power supply was connected to the reservoirs. A voltage of +1000 V was applied for 30 seconds to the sample reservoir with the detection reservoir grounded and the buffer reservoir floating, in order to facilitate the filling of the injection channel (between the separation channel and the sample reservoir).
  • the electrophoresis buffer was a phosphate buffer solution (10 mM, pH 7.3) containing 1 mM potassium chloride. Prior to use, the buffer solutions were filtered through a 0.45 ⁇ m filter (Gelman Acrodisc) and sonicated for 20 minutes. The injection was performed by applying +500 V to the sample reservoir for 3 seconds with the detection reservoir grounded and the buffer reservoir floating. The separation was performed by applying +1000 V to the buffer reservoir with the detection reservoir grounded and the sample reservoir floating.
  • FIG. 11 compares electropherograms obtained at the bare (A) and palladium-coated (B) carbon strip detectors for a mixture containing 50 ⁇ M hydrazine (a), 100 ⁇ M methylhydrazine (b), 300 ⁇ M dimethylhydrazine (c), and 150 ⁇ M phenylhydrazine (d).
  • the injection potential was +500 V, separation potential +1000 V, and detection potential +0.5 V for (B) and +0.8 V for (A).
  • Phosphate buffer (10mM and pH 7.3) was used as running buffer. Despite significantly lower operating potential (+0.50 vs.
  • the palladium-modified electrode resulted in substantially larger and sharper peaks.
  • the four peaks were well-resolved, with the entire assay requiring less than 2 minutes, with hydrazine, methylhydrazine, and dimethylhydrazine detected within less than 75 seconds; an even faster separation, 20 to 30 seconds, was achieved using higher separation voltages.
  • the data of FIG. 11 illustrate the advantages of using catalytic-modified electrode detectors for detecting high overvoltage analytes.
  • the flat baseline and low noise level also indicate an effective isolation from the high separation potential.
  • Example 14 Hydrodynamic Voltammograms for Hydrazine and Methylhydrazine The marked decrease in the overpotential for the detection of the hydrazine compounds is illustrated from the voltammetric profiles of FIG. 12, obtained using the apparatus and methods as in Example 13.
  • the figure depicts typical hydrodynamic voltammograms for the oxidation of 100 ⁇ M hydrazine (a) and methylhydrazine (b).
  • the curves were developed pointwise by making 100 MV changes in the applied potential over the -0.3 to +0.9 V range, and using a separation voltage of 1000 V. Both compounds display similar current-potential profiles, with defined waves, starting around +0.0 V, and leveling off above +0.5 V.
  • the half-wave potentials are +0.26 V. All subsequent amperometric work employed a potential of +0.5 V.
  • Example 15 Influence of Separation Potential on Hydrazine Compounds
  • the effect of the separation potential upon the amperometric response and separation efficiency is shown in FIG. 13.
  • the mixture contained 100 ⁇ M hydrazine (A) and 300 ⁇ M dimethylhydrazine (B). Separation was performed using (a) +1000 V, (b) +1500 V, (c) +2000 V, (d) +2500 V, (e) +3000 V, (f) +3500 V, and (g) +4000 V. Other conditions, as in Example 13. Also shown (inset) is the effect of separation potential upon the resolution (R) and number of apparent theoretical plates ( ⁇ /) for hydrazine.
  • the plate number decreases rapidly (from 4550 to 2230) upon raising the voltage between 1000 V and 2000 V; a slower change in the plate number (between 2230 and 950) was observed over the 2000 V to 4000 V range.
  • the resolution between the hydrazine and methylhydrazine peaks decreased from 1.65 to 0.61 upon raising the separation voltage between 1000 V and 4000 V.
  • the peak currents increased rapidly with the voltage between 1000 V and 2500 V and decreased slowly at higher voltages. Such a decrease can be attributed to the anodic shift of the hydrodynamic voltammogram that results in operation below the potential-independent transport-limited plateau region.
  • the separation voltage had a negligible effect upon the background noise level.
  • Flat baselines were observed using the low separation voltages; however, a larger initial baseline slope was observed for voltages ranging from 2500 V and 4000 V, indicating an incomplete isolation from high separation voltages.
  • Electropherograms for sample mixtures containing increasing levels of hydrazine and methylhydrazine in 2 x 10 5 M steps are shown in FIG. 14, which depicts results for mixtures containing (a) 20, (b) 40, (c) 60, (d) 80, and (e) 100 ⁇ M hydrazine (A) and methylhydrazine (B), again using conditions as in Example 13. Also shown (inset) are the resulting calibration plots over the 20 ⁇ M to 200 ⁇ M range. Defined peaks proportional to the analyte concentration were observed for both compounds.
  • the resulting calibration plots were linear with sensitivities of 0.247 and 0.188 nA/ ⁇ M for hydrazine and methylhydrazine, respectively (correlation coefficients, 0.998 and 0.996).
  • Such values are similar to those common for electrochemical detection to conventional fused-silica capillary electrophoresis.
  • Example 17 Gold-Coated Electrode for Phenolic Compound Detection An electrode was made as generally described in Example 2, with the carbon working- electrode area coated with gold by applying a pulse wave-form with a square-wave pulse potential between -0.2 and +0.75 V, versus Ag/AgCI, with a pulse width of 0.6 seconds for 30 minutes in a solution containing 300 ppm Au(lll), 0.1 M NaCl, and 1.5% HCl. Electrophoresis and detection proceeded as in Example 3, with a mixed borate/phosphate buffer, 10 mM each (pH 8.0), for separating chlorophenols or a 10 mM borate buffer (pH 10.5) for other phenols, using the device of FIG. 3.
  • a mixed borate/phosphate buffer 10 mM each (pH 8.0)
  • 10 mM borate buffer pH 10.5
  • a potential of +1500 V was applied to the sample reservoir 36 for 20 seconds to fill the injection channel, between the separation channel 20 and the sample reservoir 36, while the detection reservoir was grounded and all the other reservoirs floating.
  • the injection was effected by applying +1500 V between reservoir 36 and the grounded detection reservoir for 2 seconds. This drove the sample "plug" into the separation channel through the intersection.
  • Reservoir 32 was not used and was filled with buffer to provide equal hydrostatic levels. Separations were performed by switching the high voltage contacts and applying separation potential of +1500 V to the running buffer reservoir 34 with the detection reservoir grounded and all other reservoirs floating.
  • FIG. 15 depicts an electropherogram obtained at the gold-coated carbon strip detectors for a mixture containing (a) 100 ⁇ M phenol; (b) 100 ⁇ M 2-chlorophenol; (c) 200 ⁇ M 2,4-dichlorophenol; (d) 200 ⁇ M 2,3-dichlorophenol; (e) 200 ⁇ M 2,4,5-trichlorophenol; (f) 200 ⁇ M 2,4,6-trichlorophenol; and (g) 200 ⁇ M 2,6-dichlorophenol.
  • the raw data of electrophorograms were digitally filtered by 35-point least-square smoothing. The seven peaks were well resolved, with the entire assay requiring around 4 minutes.
  • the migration order reflects the pK a values of the individual chlorophenols.
  • FIG. 16 depicts separation and detection of phenolic compounds with high p a values and 10 mM borate buffer at pH 10.5 and a separation potential of +0.9 V. Other conditions are as in Example 17. Complete separation of 6 x 10 5 M 2,4 dimethylphenol (2,4 DMP), o-cresol (O-C), phenol (P), and 2-chlorophenol (2-CP) was obtained within 3 minutes.
  • FIG. 17 depicts hydrodynamic voltammograms of (a) 1 x 10" M phenol; (b) 1.5 x 10"* M 2,4- dichlorophenol; and (c) 3 x 10 " " M 2,4,5-trichlorophenol, with operating conditions as in Examples 17 and 18.
  • the curves were developed pointwise by making 100 mV changes in the applied potential over the +0.3 V to +1.20 V range, and using a separation voltage of 1500 V.
  • a well-defined sigmoidal response is observed for all three compounds.
  • the waves start at (a) +0.50 V or (b) +0.60 V and level off above (b) +0.90 V or (a.c) +1.0 V.
  • the half-wave potentials are (a) +0.69 V, (b) +0.76 V and (c) +0.75 V.
  • FIG. 18 depicts the influence of the separation voltage upon the response for a mixture containing 1 x 10 " " M of phenol and 2,4-dichlorophenol. Separation was performed using (a) +500 V; (b) +1000 V; (c) +1500 V; (d) +2000 V; (e) +2500 V; (f) +3000 V; (g) +3500 V; and (h) +4000 V, with other conditions as in Examples 17 and 18.
  • Increasing the separation potential from 500 to 4000 V in 500 V increments, a-h) dramatically decreased the migration time for both phenol (P) and 2,4- dichlorophenol (2,4-DCP), from 265 to 30 seconds and from 330 to 45 seconds, respectively.
  • the phenol peak width (at half height) decreased from around 8.5 seconds at 500 V to about 5.5 seconds at 4000 V. Also shown (as inset) is the effect of the separation voltage upon the separation efficiency, i.e. on the plate number (N). For both phenol and dichlorophenol the plate number increased to maximum values of 7200 and 9100, respectively, upon raising the separation potential between 500 and 1500 V, and decreases gradually (to 400) upon raising the potential to 3500 V. The maximum number of plates (9100) corresponds to a plate height of 0.0079 mm.
  • the separation voltage had a negligible effect upon the background noise level. Flat baselines were observed using the low separation voltages ( ⁇ 2000 V); however, a larger initial baseline slope is observed for voltages ranging from 2000 to 4000 V, indicating an incomplete isolation from high separation voltages.
  • FIG. 19 depicts eletropherograms for mixtures containing increasing levels of phenol and 2- chlorophenol in 2 x 10 s M steps and of 2,4-dichlorophenol in 4 x 10 5 M steps (a-e). Also shown (inset) are the resulting calibration plots. Defined peaks proportional to the analyte concentration were observed for all three compounds. The resulting calibration plots (also shown) were highly linear with sensitivities of 124.3, 11.6 and 52.6 nA/mM for phenol, 2-chlorophenol, and 2,4- dichlorophenol, respectively (correlation coefficients, 0.999, 0.998 and 0.999).
  • FIG. 20 depicts an electropherogram for a river water sample, before (A) and after (B) spiking with (a) 1 x 10 5 M phenol, (b) 2-chlorophenol, (c) 2,4-dichlorophenol, and (d) 2,3-dichlorophenol.
  • Example 22 Lack of Surface Fouling with Phenolic Compounds Amperometric detection of phenols is commonly prone to surface fouling, due to formation of inhibitory polymeric films. Using the methods of Examples 17 to 21 , no surface fouling or passivation was observed. A series of 20 repetitive injections of a 6 x 10 5 M phenol solution (using the same detector strip) resulted in a relative standard deviation (R.S.D.) of 3.7%. Similarly, a R.S.D. of 6.2% was observed for 12 successive measurements of 6 x 10 5 M 2,4 dimethylphenol. The other phenolic compounds were also subjected to repetitive injections and resulted in R.S.D.
  • Example 23 Separation Reaction Device for Simultaneous Bioassays
  • a glass microchip layout as depicted in FIG. 4 was employed for bioassays of glucose, ascorbic acid, uric acid, and acetaminophen using a glucose oxidase (GOx) enzyme system.
  • the sample and the enzyme GOx are mixed; the neutral glucose substrate and hydrogen peroxide are then separated by electrophoresis from the anionic urate and ascorbic species, which migrate at a slower rate, as depicted in the schematic diagram of FIG. 21.
  • GOx glucose oxidase
  • the enzyme (GOx)/running buffer and sample solutions are mixed at the channel intersection and in the separation channel using electrokinetic flow.
  • the enzymatic reaction occurs along the separation/reaction channel while the enzyme (in the running buffer) and glucose (in the sample plug) diffuse downstream: glucose + oxygen sss- ⁇ hydrogen peroxide + gluconic acid
  • the enzymatically liberated neutral peroxide species is electrophoretically separated from the anionic uric and ascorbic acids in the separation/reaction channel, see FIG. 21, and the three oxidizable species are detected at the downstream working electrode at different migration times.
  • a gold-coated electrode was used as in Example 17.
  • the channels of the device of FIG. 4 were treated before use by rinsing with 0.1 M sodium hydroxide and deionized water for 20 and 5 min, respectively.
  • the buffer reservoir was filled with the phosphate buffer solution, while the buffer-with-GOx reservoir was filled with phosphate buffer containing 75 U/mL glucose oxidase.
  • the sample reservoir was filled with mixtures containing glucose, uric acid, ascorbic acid, and/or acetaminophen.
  • the detection/waste reservoir was filled with the phosphate buffer solution.
  • Other reservoirs were filled with 200 ⁇ L of the corresponding solutions, thus maintaining equal hydrostatic levels.
  • the initial filling of the injection channel (between the separation channel and the sample reservoir) with the sample solution was achieved by applying a potential of +1500 V for 20 seconds to the sample reservoir with the detection reservoir grounded and other reservoirs floating.
  • the actual assays were performed by loading the sample plug into the separation/reaction channel, by applying +1500 V to the sample reservoir for 2 seconds (with the detection reservoir grounded and other reservoirs floating). Subsequently, for simultaneous measurements of glucose, uric acid, and ascorbic acid, the separation voltage was applied to the buffer-with-GOx reservoir. Mixing of the glucose substrate (in the sample plug) with the enzyme (in the running buffer) started at the intersection and proceeded primarily down in the separation channel. The neutral hydrogen peroxide species (produced in the separation/reaction channel) and the uric and ascorbic acids were separated in the separation/reaction channel of FIG. 4, and the three oxidizable species were detected amperometrically at different migration times.
  • measurements of glucose and acetaminophen were carried out by comparing the responses with and without the enzyme.
  • a total signal was measured with the running buffer containing GOx, while the acetaminophen signal alone was recorded by applying the separation voltage to the buffer reservoir (containing no GOx). The current difference was used for quantifying the glucose concentration in the sample mixture.
  • the electropherograms were recorded with a time resolution of 0.1 seconds while the detection potential was applied (usually +0.9 V vs Ag/AgCI wire). Sample injections were perfonmed after stabilization of the baseline. No software filtration of the signal was used. All bioassays were carried out at room temperature.
  • Acetaminophen a common neutral interferent, is carried solely by the electroosmotic flow and cannot be resolved from the neutral glucose/peroxide species.
  • electropherograms as shown in FIG. 23 were obtained in the presence (A, B, D) and absence (C) of GOx in the running buffer.
  • Sample solutions were (A) 1 x 10 3 M glucose, (B) 1 x 10 3 M glucose and 1 x 10 4 M acetaminophen; and (C, D) 1 x 10 " " M acetaminophen.
  • Example 24 Using the method of Example 24 with the device of Example 23, the influence of the separation potential upon the separation efficiency and overall performance was evaluated.
  • the sample mixture contained 1 x 10 3 M glucose, 6 x 10 "4 M ascorbic acid, and 4 x 10 " " M uric acid.
  • Separation voltages were (a) +1000, (b) +1500, (c) +2000, (d) +2500, and (e) +3000 V.
  • Increasing the separation potential from 1000 to 3000 V (in 500 V increments, a-e) dramatically decreased the migration time for glucose from 135 to 45 seconds.
  • the corresponding times for ascorbic and uric acids were reduced from 330 and 360 to 105 and 115 seconds, respectively.
  • the separation efficiency represented by the plate number, decreased from 6000 to 1100 (for ascorbic acid) and from 5200 to 1050 (for uric acid) upon raising the separation potential from 1000 to 2500 V.
  • FIG. 25 depicts the effect of the GOx level in the reagent solution upon the response to the 1 x 10 3 M glucose substrate
  • the current increased rapidly upon raising the GOx concentration between 0 and 50 U/mL, then increased more slowly, and finally started to level off above 125 U/mL
  • All subsequent work employed 75 U/mL GOx Enzyme levels higher than 100 U/mL resulted in increased background noise and absorption onto the channel walls
  • Hydrodynamic voltammograms i e , plots of current response versus the applied potential
  • the gold- coated carbon detector displayed a defined wave-shaped voltammogram for glucose, with the current starting at +0 50 V and leveling off above +0 80 V
  • Most work employed a detection potential of +0 90 V, in view of the high background noise above +1 0 V
  • the bare carbon surface required higher potentials for the peroxide detection, with the current starting at +0 80 V and a plateau above +1 20 V
  • Example 29 Run-to-Run Variations in Injection Time Using the method of Example 24 with the device of Example 23, the run-to-run variation in injection time was evaluated Results are shown in FIG. 26, which depicts reproducibility of the current response for 1 x 10 3 M glucose (a) and 5 x 10" M u ⁇ c acid (b) and of the glucose-to-unc acid peak ratio (c) Asterisks denote the use of deliberately shorter sample injection times As shown in FIG. 26, use of u ⁇ c acid as a "built-in" internal standard greatly improved the reproducibility of repetitive glucose measurements in connection with measurements of the glucose/urate peak ratio. Both the glucose and uric acid peaks yielded relative standard deviations of 10.6 and 10.5%, respectively; an R.S.D. of 4.2% was estimated for the glucose/urate peak ratio.
  • Example 24 electrophoretic peaks for increasing levels of glucose (A), ascorbic acid (B), and uric acid (C) in 1 x 10 " * M steps (a - e), as shown in FIG. 27.
  • Highly linear calibration plots were observed for both ascorbic and uric acids (see insets), with slopes of 21.6 and 21.8 nA/mM (and correlation coefficients r of 0.998 and 0.999, respectively).
  • the response for the glucose substrate displayed a curvature at concentrations higher than 7 x 10" M.
  • Example 31 Apparatus and Protocol with Pre-Column Reactor
  • Example 2 was employed, including a reagent reservoir R, a sample reservoir S, a running buffer reservoir RB, and a buffer reservoir B
  • a reaction chamber RC 200 ⁇ m wide and 3 6 mm long was connected through 50 ⁇ m wide channels to the reagent and sample reservoirs at one side, and to a four-way injection cross at the other side The injection cross was followed by a 74 mm long, 50 ⁇ m wide, separation channel Otherwise, the apparatus was as described in Example 2, with a gold-coated carbon working electrode area as in Example 17
  • the reagent reservoir R was filled with 80 ⁇ L of an o-phthalaldehyde (OPA), 2-mercaptoethanol (2ME) reagent solution, while the sample reservoir S was filled with 80 ⁇ L of mixture of ammo acids
  • OPA o-phthalaldehyde
  • 2ME 2-mercaptoethanol
  • the two buffer reservoirs B and RB were filled with 70 ⁇ L volume of the electrophoresis buffer
  • a voltage of +1500 V was applied for 60 seconds to the reagent and sample reservoirs with the detection reservoir grounded and other reservoirs floating, in order to fill the reaction chamber and assure a constant mixing ratio
  • the sample and reagent solutions were loaded electrokmetically into the reaction chamber and mixed together by dispersion
  • the derivatization reaction of ammo acids with OPA occurred in the reaction chamber upon mixing the reagent electrophoresis buffer with the sample, located in the sample reservoir which produced the OPA-ammo a ⁇ d denvative dunng the path flowing through the chamber
  • reaction-product "plug” was loaded into the separation channel by applying +1500 V to both sample and reagent reservoirs for 3 seconds with the detection reservoir grounded and the other reservoirs floating
  • the injection time of 3 seconds corresponded to an injected volume of 2 nL Separation was usually performed by applying +2000 V to the running-buffer reservoir with the detection reservoir grounded and the other reservoirs floating Amperomet ⁇ c signals of different ammo acids were detected at the detection reservoir at different elution times
  • Example 32 Electropherograms obtained at the Gold-Coated Carbon Working Electrode Using the device and methods of Example 31 , an electrophoresis buffer was made consisting of 20mM borate buffer containing 30mM dodecyl sodium sulfate (SDS) at pH 9.4. As shown in FIG.
  • an electropherogram was obtained of a mixture containing 1.0x10 " " M (b) histidine, (c) valine, (d) isoleucine, (e) leucine, 2.0x10-4M (f) glutamic acid, (g) aspartic acid, (h) arginine, and (i) lysine, with (a) corresponding to the excess of the 2-ME reagent.
  • An injection potential of +1500 V, separation potential of +2000 V, injection time of 3 seconds, and detection potential of + 0.8 V were employed.
  • the reagent solution was 4.8x10 3 M OPA and 4.2x10 3 M 2ME.
  • the eight amino acids peaks were well resolved, with the entire assay requiring around six minutes; the first four amino acids are detected within less than three minutes (peaks b-e).
  • the flat baseline and low noise level indicated an effective isolation from the driving voltage.
  • Example 31 The methods of Example 31 were employed to determine the effect of the detector potential using hydrodynamic voltammograms as shown in FIG. 29.
  • 2x10 "4 M valine (a), glutamic acid (b), and arginine (c) were employed, with a reagent solution consisting of 2.4x10 3 M OPA and 2.1x10 3 M 2ME.
  • Similar profiles were observed for the three amino acids, reflecting the detection of the corresponding isoindole reaction products.
  • the oxidation started at +0.50 V, with a maximum response observed in the vicinity of +0.90V.
  • Subsequent analytical work was performed with a potential of +0.80 V that offered the most favorable signal-to-background characteristics.
  • the different voltammetric profiles and sensitivity trend (valine>glutamic acid>arginine) of FIG. 29 are related to the chemical structure of the amino-acid residue of the isoindole products.
  • Example 34 Effect of Driving Voltage on Amino Acid Detection Using the methods of Example 31 the effect of varying the driving voltage is depicted in
  • FIG. 30 1.5X10 "4 M histidine (b), valine (c) and isoleucine (d) were used, with separations performed using (A) +1000, (B) +1500, (C) +2000, (D) +2500, and (E) +3000 V, and reagent solution consisting of 2.4x10 "3 M OPA and 2.1x10 "3 M 2ME.
  • the increase in the electrical field decreased the migration time for histidine, valine, and isoleucine from 242, 260, and 278 seconds to 70, 76, and 91 seconds, respectively. This decrease is in agreement with the linear dependence between the applied field strength and the migration velocity obtained for all three analytes (not shown).
  • the peak widths at half height also decreased upon increasing the driving voltage, e.g., from 6.1 seconds at 1000 V to about 2.3 seconds at 2500 V in the case of histidine.
  • the decreased separation efficiency at higher fields is indicated from the decrease in the theoretical plate number for histidine from 9,900 at 1000 V to 2900 at 3000 V.
  • Example 31 Using the methods of Example 31 , amino acids of Example 32, and other operating conditions as in Example 33, stepping of the driving voltage for decreasing the migration time of late- eluting components and the overall analysis time was examined.
  • FIG. 31 (A) depicts constant separation voltage of +1500 V and (B) stepping up the separation voltage to +3000 V after 200 seconds of separation at a separation voltage of +1500 V.
  • stepping the voltage from +1500 to +3000V after the initial after 200 seconds, a complete run is accomplished within 320 seconds, rather than the 470 seconds required under a constant field strength, thereby reducing the overall analysis time by about 150 seconds.
  • Example 36 Changing Ratios of Derivatization Reaction Constituents
  • the derivatization reaction can be altered by controlling the electrical fields in the sample and Reagent arms, and by changing the relative concentrations of the OPA and 2ME reagents.
  • the influence of the reagent concentration was examined by varying the concentration of OPA and 2ME with a constant level of the amino acids, as shown in FIG. 32, (A) and (B).
  • the current signals for histidine (a), valine (b), and leucine (c) increased rapidly upon raising the OPA concentration between 0 and 1.6x10 3 M, and nearly leveled off at higher reagent concentrations (A).
  • FIG. 33 displays the effect of the sample/reagent mixing ratio upon the response for a mixture of three amino acids.
  • 2.0x10 "4 M valine (a), isoleucine (b), and leucine (c) were employed, with +1500 V applied to the sample reservoir while the voltage applied to the reagent reservoir was changed from +1390 to +1470 V by placing different resistors between the +1500 V power-supply terminal and the reagent reservoir.
  • the mixing ratio was calculated based on measuring the ratio of currents flowing through the respective reservoirs. For all analytes, the response rose upon increasing the sample/reagent ratio in the reaction chamber from 1.0 to 2.2, after which it decreases slightly.
  • Example 37 Concentration Dependence of Amino Acid Detection
  • the amperometric detector system and method of Example 31 displayed well-defined concentration dependence. This was examined by recording electropherograms for sample mixtures containing increasing levels of histidine and isoleucine or valine and leucine in ten steps of 2x10 "5 M, with defined peaks, proportional to the analyte concentration, observed for all four compounds.
  • the resulting calibration plots were highly linear with sensitivities of 50.6, 64.1 , 41.0, and 59.1 nA/mM for histidine, valine, isoleucine, and leucine, respectively (correlation coefficients, 0.992, 0.999, 0.996 and 0.995).
  • the high sensitivity of the amperometric detector is coupled to a low noise level that resulted in low detection limits of 2.5x10 "6 M for valine and 2.7x10 "6 M for leucine, based on three standard deviations of the noise in assays of a mixture containing 2x10 "5 M of these compounds.
  • Such values correspond to 5.0 and 5.4 fmol valine and leucine, respectively, (i.e., 590 and 710 fg) in the 2 nL injection plugs.
  • Excess concentrations of OPA and 2ME is required to attain such micromolar detection limits, such that the reagent concentration is not limiting the derivatization reaction.
  • Example 1 The device of Example 1 and methods of Example 3 are employed.
  • a DNA separation matrix is utilized, such as hydroxyethylcellulose.
  • Injection is performed by applying voltage to the sample reservoir for a suitable period of time with the detection reservoir grounded and the buffer reservoir floating. Separation is carried out by applying a separation voltage. Detection is by amperometric means, using an electrode of Example 2.

Landscapes

  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Chemical & Material Sciences (AREA)
  • Molecular Biology (AREA)
  • Analytical Chemistry (AREA)
  • Chemical Kinetics & Catalysis (AREA)
  • Electrochemistry (AREA)
  • Physics & Mathematics (AREA)
  • Biochemistry (AREA)
  • General Health & Medical Sciences (AREA)
  • General Physics & Mathematics (AREA)
  • Immunology (AREA)
  • Pathology (AREA)
  • Dispersion Chemistry (AREA)
  • Apparatus Associated With Microorganisms And Enzymes (AREA)
  • Investigating Or Analysing Biological Materials (AREA)

Abstract

Appareil destiné à effectuer des processus et des analyses microfluidiques, qui comporte au moins un canal allongé microfluidique (20, 130), un moyen destiné au transport de fluides dans le canal microfluidique et au moins une électrode (104, 142) à film épais se trouvant en connexion fluidique avec l'orifice de sortie terminal (25, 132) du canal microfluidique. La présente invention concerne en outre un microsystème combiné sur puce de réaction, séparation et détection électrochimique à film épais, destiné à être utilisé pour la détection d'une large gamme d'analytes, ainsi que des procédés d'utilisation dudit microsystème.
PCT/US2000/030422 1999-11-05 2000-11-03 Dispositifs microfluidiques avec detection electrochimique a film epais WO2001035088A1 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
AU22490/01A AU2249001A (en) 1999-11-05 2000-11-03 Microfluidic devices with thick-film electrochemical detection

Applications Claiming Priority (4)

Application Number Priority Date Filing Date Title
US16385299P 1999-11-05 1999-11-05
US60/163,852 1999-11-05
US09/705,100 US6878255B1 (en) 1999-11-05 2000-11-02 Microfluidic devices with thick-film electrochemical detection
US09/705,100 2000-11-02

Publications (1)

Publication Number Publication Date
WO2001035088A1 true WO2001035088A1 (fr) 2001-05-17

Family

ID=26860002

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/US2000/030422 WO2001035088A1 (fr) 1999-11-05 2000-11-03 Dispositifs microfluidiques avec detection electrochimique a film epais

Country Status (3)

Country Link
US (1) US6878255B1 (fr)
AU (1) AU2249001A (fr)
WO (1) WO2001035088A1 (fr)

Cited By (10)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2005093388A1 (fr) * 2004-03-26 2005-10-06 Infectio Recherche Inc. Pile amovible a ecoulement microfluidique
WO2007096730A1 (fr) * 2006-02-21 2007-08-30 Universal Biosensors Pty Ltd. Mecanisme de transfert de fluide
US7402616B2 (en) 2004-09-30 2008-07-22 Lifescan, Inc. Fusible conductive ink for use in manufacturing microfluidic analytical systems
WO2009059022A1 (fr) 2007-10-30 2009-05-07 Complete Genomics, Inc. Appareil pour le séquençage rapide d'acides nucléiques
EP2623975A3 (fr) * 2006-12-26 2013-10-23 Sekisui Chemical Co., Ltd. Procédé de mesure du taux d'hémoglobine et de glucose et appareil d'électrophorèse
WO2015167990A1 (fr) * 2014-04-29 2015-11-05 Battelle Memorial Institute Injecteurs d'échantillons microfluidiques sans injection électrocinétique
US9551026B2 (en) 2007-12-03 2017-01-24 Complete Genomincs, Inc. Method for nucleic acid detection using voltage enhancement
US9803239B2 (en) 2012-03-29 2017-10-31 Complete Genomics, Inc. Flow cells for high density array chips
CN114034749A (zh) * 2021-11-09 2022-02-11 鲁东大学 检测多种生物小分子的微型电化学传感器及其制作方法
US11835437B2 (en) 2011-11-02 2023-12-05 Complete Genomics, Inc. Treatment for stabilizing nucleic acid arrays

Families Citing this family (128)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6036924A (en) 1997-12-04 2000-03-14 Hewlett-Packard Company Cassette of lancet cartridges for sampling blood
US6391005B1 (en) 1998-03-30 2002-05-21 Agilent Technologies, Inc. Apparatus and method for penetration with shaft having a sensor for sensing penetration depth
DE10057832C1 (de) 2000-11-21 2002-02-21 Hartmann Paul Ag Blutanalysegerät
US8641644B2 (en) 2000-11-21 2014-02-04 Sanofi-Aventis Deutschland Gmbh Blood testing apparatus having a rotatable cartridge with multiple lancing elements and testing means
US7041068B2 (en) 2001-06-12 2006-05-09 Pelikan Technologies, Inc. Sampling module device and method
EP1406537B1 (fr) 2001-06-12 2011-01-12 Pelikan Technologies Inc. Systeme integre de prelevement et d'analyse d'echantillons sanguins avec module de prelevement a utilisation multiple
WO2002100254A2 (fr) 2001-06-12 2002-12-19 Pelikan Technologies, Inc. Procede et appareil pour un dispositif de lancement de lancette integre sur une cartouche de prelevement de sang
US7981056B2 (en) 2002-04-19 2011-07-19 Pelikan Technologies, Inc. Methods and apparatus for lancet actuation
US7344507B2 (en) 2002-04-19 2008-03-18 Pelikan Technologies, Inc. Method and apparatus for lancet actuation
US7699791B2 (en) 2001-06-12 2010-04-20 Pelikan Technologies, Inc. Method and apparatus for improving success rate of blood yield from a fingerstick
US9795747B2 (en) 2010-06-02 2017-10-24 Sanofi-Aventis Deutschland Gmbh Methods and apparatus for lancet actuation
US9226699B2 (en) 2002-04-19 2016-01-05 Sanofi-Aventis Deutschland Gmbh Body fluid sampling module with a continuous compression tissue interface surface
US8337419B2 (en) 2002-04-19 2012-12-25 Sanofi-Aventis Deutschland Gmbh Tissue penetration device
US7033371B2 (en) 2001-06-12 2006-04-25 Pelikan Technologies, Inc. Electric lancet actuator
US9427532B2 (en) 2001-06-12 2016-08-30 Sanofi-Aventis Deutschland Gmbh Tissue penetration device
CA2448902C (fr) 2001-06-12 2010-09-07 Pelikan Technologies, Inc. Autopiqueur a optimisation automatique presentant des moyens d'adaptation aux variations temporelles des proprietes cutanees
AU2002312521A1 (en) 2001-06-12 2002-12-23 Pelikan Technologies, Inc. Blood sampling apparatus and method
US7344894B2 (en) 2001-10-16 2008-03-18 Agilent Technologies, Inc. Thermal regulation of fluidic samples within a diagnostic cartridge
KR100438828B1 (ko) * 2001-11-08 2004-07-05 삼성전자주식회사 칩 상의 전기적 미세 검출기
US7141058B2 (en) 2002-04-19 2006-11-28 Pelikan Technologies, Inc. Method and apparatus for a body fluid sampling device using illumination
US9795334B2 (en) 2002-04-19 2017-10-24 Sanofi-Aventis Deutschland Gmbh Method and apparatus for penetrating tissue
US7291117B2 (en) 2002-04-19 2007-11-06 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US8267870B2 (en) 2002-04-19 2012-09-18 Sanofi-Aventis Deutschland Gmbh Method and apparatus for body fluid sampling with hybrid actuation
US7976476B2 (en) 2002-04-19 2011-07-12 Pelikan Technologies, Inc. Device and method for variable speed lancet
US7563232B2 (en) 2002-04-19 2009-07-21 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7374544B2 (en) 2002-04-19 2008-05-20 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7892183B2 (en) 2002-04-19 2011-02-22 Pelikan Technologies, Inc. Method and apparatus for body fluid sampling and analyte sensing
US7229458B2 (en) 2002-04-19 2007-06-12 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7297122B2 (en) 2002-04-19 2007-11-20 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7410468B2 (en) 2002-04-19 2008-08-12 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7717863B2 (en) 2002-04-19 2010-05-18 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7331931B2 (en) 2002-04-19 2008-02-19 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7901362B2 (en) 2002-04-19 2011-03-08 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7674232B2 (en) 2002-04-19 2010-03-09 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7226461B2 (en) 2002-04-19 2007-06-05 Pelikan Technologies, Inc. Method and apparatus for a multi-use body fluid sampling device with sterility barrier release
US8221334B2 (en) 2002-04-19 2012-07-17 Sanofi-Aventis Deutschland Gmbh Method and apparatus for penetrating tissue
US7491178B2 (en) 2002-04-19 2009-02-17 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US9248267B2 (en) 2002-04-19 2016-02-02 Sanofi-Aventis Deustchland Gmbh Tissue penetration device
US7524293B2 (en) 2002-04-19 2009-04-28 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US9314194B2 (en) 2002-04-19 2016-04-19 Sanofi-Aventis Deutschland Gmbh Tissue penetration device
US7371247B2 (en) 2002-04-19 2008-05-13 Pelikan Technologies, Inc Method and apparatus for penetrating tissue
US8784335B2 (en) 2002-04-19 2014-07-22 Sanofi-Aventis Deutschland Gmbh Body fluid sampling device with a capacitive sensor
US7582099B2 (en) 2002-04-19 2009-09-01 Pelikan Technologies, Inc Method and apparatus for penetrating tissue
US8702624B2 (en) 2006-09-29 2014-04-22 Sanofi-Aventis Deutschland Gmbh Analyte measurement device with a single shot actuator
US8579831B2 (en) 2002-04-19 2013-11-12 Sanofi-Aventis Deutschland Gmbh Method and apparatus for penetrating tissue
US7481776B2 (en) 2002-04-19 2009-01-27 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7909778B2 (en) 2002-04-19 2011-03-22 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7547287B2 (en) 2002-04-19 2009-06-16 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7648468B2 (en) 2002-04-19 2010-01-19 Pelikon Technologies, Inc. Method and apparatus for penetrating tissue
US7232451B2 (en) 2002-04-19 2007-06-19 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US8574895B2 (en) 2002-12-30 2013-11-05 Sanofi-Aventis Deutschland Gmbh Method and apparatus using optical techniques to measure analyte levels
GB2398751A (en) * 2003-02-28 2004-09-01 Univ Surrey A dielectrophoretic separation device
EP1633235B1 (fr) 2003-06-06 2014-05-21 Sanofi-Aventis Deutschland GmbH Appareil d'echantillonnage de fluides anatomiques et d'examen de l'analysat
WO2006001797A1 (fr) 2004-06-14 2006-01-05 Pelikan Technologies, Inc. Element penetrant peu douloureux
EP1635700B1 (fr) 2003-06-13 2016-03-09 Sanofi-Aventis Deutschland GmbH Appareil pour dispositif d'analyse sur le lieu de soin
US8282576B2 (en) 2003-09-29 2012-10-09 Sanofi-Aventis Deutschland Gmbh Method and apparatus for an improved sample capture device
JP4121928B2 (ja) * 2003-10-08 2008-07-23 シャープ株式会社 太陽電池の製造方法
WO2005037095A1 (fr) 2003-10-14 2005-04-28 Pelikan Technologies, Inc. Procede et appareil fournissant une interface-utilisateur variable
US7822454B1 (en) 2005-01-03 2010-10-26 Pelikan Technologies, Inc. Fluid sampling device with improved analyte detecting member configuration
EP1706026B1 (fr) 2003-12-31 2017-03-01 Sanofi-Aventis Deutschland GmbH Procédé et appareil permettant d'améliorer le flux fluidique et le prélèvement d'échantillons
EP1751546A2 (fr) 2004-05-20 2007-02-14 Albatros Technologies GmbH & Co. KG Hydrogel imprimable pour biocapteurs
WO2005120365A1 (fr) 2004-06-03 2005-12-22 Pelikan Technologies, Inc. Procede et appareil pour la fabrication d'un dispositif d'echantillonnage de liquides
US8652831B2 (en) 2004-12-30 2014-02-18 Sanofi-Aventis Deutschland Gmbh Method and apparatus for analyte measurement test time
US20060163083A1 (en) * 2005-01-21 2006-07-27 International Business Machines Corporation Method and composition for electro-chemical-mechanical polishing
ZA200707354B (en) * 2005-03-08 2009-04-29 Authentix Inc Microfluidic device for identification, quantification, and authentication of latent markers
US20080178692A1 (en) * 2007-01-29 2008-07-31 Searete Llc, A Limited Liability Corporation Of The State Of Delaware Fluidic methods
US20070217076A1 (en) * 2006-03-15 2007-09-20 Seagate Technology Llc Nanoscale machined electrode and workpiece, and method of making the same
US7625468B2 (en) * 2006-03-15 2009-12-01 Seagate Technology, Llc Electrode for electrochemical machining
US20100024908A1 (en) * 2006-11-27 2010-02-04 Takashi Yasuda Microvolume liquid dispensing device
JP5103614B2 (ja) * 2006-11-27 2012-12-19 国立大学法人九州工業大学 微量液体分取デバイス
US11339430B2 (en) 2007-07-10 2022-05-24 Life Technologies Corporation Methods and apparatus for measuring analytes using large scale FET arrays
US8262900B2 (en) 2006-12-14 2012-09-11 Life Technologies Corporation Methods and apparatus for measuring analytes using large scale FET arrays
WO2008076406A2 (fr) 2006-12-14 2008-06-26 Ion Torrent Systems Incorporated Procédés et appareil permettant de mesurer des analytes en utilisant des matrices de tec à grande échelle
US20090050569A1 (en) * 2007-01-29 2009-02-26 Searete Llc, A Limited Liability Corporation Of The State Of Delaware Fluidic methods
US10001496B2 (en) * 2007-01-29 2018-06-19 Gearbox, Llc Systems for allergen detection
US8617903B2 (en) * 2007-01-29 2013-12-31 The Invention Science Fund I, Llc Methods for allergen detection
US20080181821A1 (en) * 2007-01-29 2008-07-31 Searete Llc, A Limited Liability Corporation Of The State Of Delaware Microfluidic chips for allergen detection
US20080180259A1 (en) * 2007-01-29 2008-07-31 Searete Llc, A Limited Liability Corporation Of The State Of Delaware Devices for allergen detection
US20080245740A1 (en) * 2007-01-29 2008-10-09 Searete Llc, A Limited Liability Corporation Of The State Of Delaware Fluidic methods
US20080181816A1 (en) * 2007-01-29 2008-07-31 Searete Llc, A Limited Liability Corporation Systems for allergen detection
JP5600434B2 (ja) * 2007-04-27 2014-10-01 アークレイ株式会社 分析チップおよび分析装置
ES2716199T3 (es) * 2007-06-29 2019-06-11 Arizona Board Of Regents Acting For And On Behalf Of Arizona State Univ Sistema y método para la detección electroquímica de especies de sílice
JP2011516856A (ja) * 2008-04-04 2011-05-26 アリゾナ・ボード・オブ・リージェンツ・フォー・アンド・オン・ビハーフ・オブ・アリゾナ・ステイト・ユニバーシティー 液体中の多数の重金属イオンの同時電気化学的検出
WO2009126900A1 (fr) 2008-04-11 2009-10-15 Pelikan Technologies, Inc. Procédé et appareil pour dispositif de détection d’analyte
US20100137143A1 (en) 2008-10-22 2010-06-03 Ion Torrent Systems Incorporated Methods and apparatus for measuring analytes
US20100301398A1 (en) 2009-05-29 2010-12-02 Ion Torrent Systems Incorporated Methods and apparatus for measuring analytes
US9375169B2 (en) 2009-01-30 2016-06-28 Sanofi-Aventis Deutschland Gmbh Cam drive for managing disposable penetrating member actions with a single motor and motor and control system
WO2010131514A1 (fr) * 2009-05-15 2010-11-18 コニカミノルタオプト株式会社 Micropuce
US8776573B2 (en) 2009-05-29 2014-07-15 Life Technologies Corporation Methods and apparatus for measuring analytes
US20110065101A1 (en) 2009-06-04 2011-03-17 Lockheed Martin Corporation Multiple-sample microfluidic chip for DNA analysis
WO2011106098A2 (fr) 2010-02-25 2011-09-01 Advanced Microlabs, Llc Interface microfluidique destinée à une micropuce
US8965476B2 (en) 2010-04-16 2015-02-24 Sanofi-Aventis Deutschland Gmbh Tissue penetration device
TW201716791A (zh) 2010-06-30 2017-05-16 生命技術公司 用於測試離子感測場效電晶體（ｉｓｆｅｔ）陣列之裝置及方法
US8455927B2 (en) 2010-06-30 2013-06-04 Life Technologies Corporation One-transistor pixel array with cascoded column circuit
CN103154718B (zh) 2010-06-30 2015-09-23 生命科技公司 感测离子的电荷堆积电路和方法
US11307166B2 (en) 2010-07-01 2022-04-19 Life Technologies Corporation Column ADC
WO2012006222A1 (fr) 2010-07-03 2012-01-12 Life Technologies Corporation Capteur chimiquement sensible doté de drains légèrement dopés
US9618475B2 (en) 2010-09-15 2017-04-11 Life Technologies Corporation Methods and apparatus for measuring analytes
US20150041396A1 (en) * 2010-09-23 2015-02-12 Battelle Memorial Institute System and method of preconcentrating analytes in a microfluidic device
WO2012051529A1 (fr) 2010-10-15 2012-04-19 Lockheed Martin Corporation Conception optique microfluidique
US9970984B2 (en) 2011-12-01 2018-05-15 Life Technologies Corporation Method and apparatus for identifying defects in a chemical sensor array
US9322054B2 (en) 2012-02-22 2016-04-26 Lockheed Martin Corporation Microfluidic cartridge
TWI456196B (zh) 2012-04-24 2014-10-11 Ind Tech Res Inst 檢體免疫分析檢測裝置
US8786331B2 (en) 2012-05-29 2014-07-22 Life Technologies Corporation System for reducing noise in a chemical sensor array
EP2939011A4 (fr) 2012-12-27 2016-11-23 Senova Systems Inc Ph-mètre
US9080968B2 (en) 2013-01-04 2015-07-14 Life Technologies Corporation Methods and systems for point of use removal of sacrificial material
US9841398B2 (en) 2013-01-08 2017-12-12 Life Technologies Corporation Methods for manufacturing well structures for low-noise chemical sensors
TWI498552B (zh) 2013-01-14 2015-09-01 Nat Univ Chung Hsing 可拋式毛細管電泳檢測儀器
US8963216B2 (en) 2013-03-13 2015-02-24 Life Technologies Corporation Chemical sensor with sidewall spacer sensor surface
US20140264471A1 (en) 2013-03-15 2014-09-18 Life Technologies Corporation Chemical device with thin conductive element
WO2014149780A1 (fr) 2013-03-15 2014-09-25 Life Technologies Corporation Capteur chimique à surfaces de capteur cohérentes
US9835585B2 (en) 2013-03-15 2017-12-05 Life Technologies Corporation Chemical sensor with protruded sensor surface
US20140336063A1 (en) 2013-05-09 2014-11-13 Life Technologies Corporation Windowed Sequencing
US10458942B2 (en) 2013-06-10 2019-10-29 Life Technologies Corporation Chemical sensor array having multiple sensors per well
WO2015143307A1 (fr) * 2014-03-20 2015-09-24 The University Of Akron Capteurs tactiles souples et procédé de fabrication
WO2016049552A1 (fr) * 2014-09-26 2016-03-31 Abbott Point Of Care Inc. Identification de dispositif de cartouche pour analyses de coagulation dans des échantillons de fluide
WO2016049506A1 (fr) 2014-09-26 2016-03-31 Abbott Point Of Care Inc. Capteurs pour le dosage de la coagulation dans des échantillons de fluides
CN107110875A (zh) 2014-09-26 2017-08-29 雅培医护站股份有限公司 用在凝固测定中的鞣花酸制剂
ES2911898T3 (es) 2014-09-26 2022-05-23 Abbott Point Of Care Inc Dispositivo de cartucho de canal único para ensayos de coagulación de sangre en muestras de fluidos
CN106999932A (zh) 2014-09-26 2017-08-01 雅培医护站股份有限公司 用于流体样本中的凝结测定的具有流体结的盒设备
EP3197602B1 (fr) 2014-09-26 2021-09-01 Abbott Point Of Care, Inc. Dispositif microfabriqué avec des capteurs de microenvironnement pour analyser la coagulation dans des échantillons fluides
US10077472B2 (en) 2014-12-18 2018-09-18 Life Technologies Corporation High data rate integrated circuit with power management
US10605767B2 (en) 2014-12-18 2020-03-31 Life Technologies Corporation High data rate integrated circuit with transmitter configuration
GB2533386B (en) 2014-12-18 2019-09-11 Smiths Detection Watford Ltd A detection apparatus with pneumatic interface
WO2018122856A1 (fr) 2016-12-29 2018-07-05 Dalibor Hodko Puce électrophorétique pour applications électrophorétiques
PT3575782T (pt) * 2018-05-31 2023-08-23 Univ Del Pais Vasco/Euskal Herriko Unibertsitatea Método e dispositivo para a deteção e monitorização de uma incrustação de superfície
US11366030B2 (en) 2018-11-16 2022-06-21 The University Of Akron Flexible tactile sensors
CN113551964A (zh) * 2021-08-26 2021-10-26 德阳市人民医院 一种微流控装置及其制备方法、应用

Citations (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO1998009161A1 (fr) * 1996-08-26 1998-03-05 The Regents Of The University Of California Detecteur electrochimique integre a des puces pour electrophorese capillaire fabriquees par micro-usinage

Family Cites Families (13)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4908112A (en) 1988-06-16 1990-03-13 E. I. Du Pont De Nemours & Co. Silicon semiconductor wafer for analyzing micronic biological samples
US6001229A (en) 1994-08-01 1999-12-14 Lockheed Martin Energy Systems, Inc. Apparatus and method for performing microfluidic manipulations for chemical analysis
US5872010A (en) * 1995-07-21 1999-02-16 Northeastern University Microscale fluid handling system
US5846727A (en) 1996-06-06 1998-12-08 Board Of Supervisors Of Louisiana State University And Agricultural & Mechanical College Microsystem for rapid DNA sequencing
US6063259A (en) 1996-06-11 2000-05-16 New Mexico State University Technology Transfer Corporation Microfabricated thick-film electrochemical sensor for nucleic acid determination
US5906723A (en) 1996-08-26 1999-05-25 The Regents Of The University Of California Electrochemical detector integrated on microfabricated capillary electrophoresis chips
US6110343A (en) * 1996-10-04 2000-08-29 Lockheed Martin Energy Research Corporation Material transport method and apparatus
US5904824A (en) 1997-03-07 1999-05-18 Beckman Instruments, Inc. Microfluidic electrophoresis device
CN1105914C (zh) 1997-04-25 2003-04-16 卡钳技术有限公司 改进了通道几何结构的微型流体装置
US6207031B1 (en) * 1997-09-15 2001-03-27 Whitehead Institute For Biomedical Research Methods and apparatus for processing a sample of biomolecular analyte using a microfabricated device
US6251343B1 (en) * 1998-02-24 2001-06-26 Caliper Technologies Corp. Microfluidic devices and systems incorporating cover layers
US6274089B1 (en) * 1998-06-08 2001-08-14 Caliper Technologies Corp. Microfluidic devices, systems and methods for performing integrated reactions and separations
US6103199A (en) 1998-09-15 2000-08-15 Aclara Biosciences, Inc. Capillary electroflow apparatus and method

Patent Citations (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO1998009161A1 (fr) * 1996-08-26 1998-03-05 The Regents Of The University Of California Detecteur electrochimique integre a des puces pour electrophorese capillaire fabriquees par micro-usinage

Non-Patent Citations (5)

* Cited by examiner, † Cited by third party
Title
HENRY CHARLES S. ET AL.: "Ceramic microchips for capillary electrophoresis-electrochemistry", ANAL. COMMUN., vol. 36, 1999, pages 305 - 307, XP002938460 *
HILMI ABDELKADER ET AL.: "Electrochemical detectors prepared by electroless deposition for microfabricated electrophoresis chips", ANALYTICAL CHEMISTRY, vol. 72, no. 19, 1 October 2000 (2000-10-01), pages 4577 - 4682, XP002938464 *
ROSSIER JOEL S. ET AL.: "Microchannel networks for electrophoretic separations", ELECTROPHORESIS, vol. 20, 1999, pages 727 - 731, XP002938461 *
WANG JOSEPH ET AL.: "Integrated electrophoresis chips/amperometric detection with sputtered gold working electrodes", ANALYTICAL CHEMISTRY, vol. 71, no. 17, 1 September 1999 (1999-09-01), pages 3901 - 3904, XP002938462 *
WANG JOSEPH ET AL.: "Micromachined electrophoresis chips with thick-film electrochemical detectors", ANALYTICAL CHEMISTRY, vol. 71, no. 23, 1 December 1999 (1999-12-01), pages 5436 - 5440, XP002938463 *

Cited By (16)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2005093388A1 (fr) * 2004-03-26 2005-10-06 Infectio Recherche Inc. Pile amovible a ecoulement microfluidique
US8444934B2 (en) 2004-03-26 2013-05-21 Universite Laval Removable microfluidic flow cell
US7402616B2 (en) 2004-09-30 2008-07-22 Lifescan, Inc. Fusible conductive ink for use in manufacturing microfluidic analytical systems
WO2007096730A1 (fr) * 2006-02-21 2007-08-30 Universal Biosensors Pty Ltd. Mecanisme de transfert de fluide
US8182765B2 (en) 2006-02-21 2012-05-22 Universal Biosensors Pty Ltd Fluid transfer mechanism
US9017536B2 (en) 2006-12-26 2015-04-28 Sekisui Chemical Co., Ltd. Hemoglobin measurement method and electrophoresis apparatus
EP2623975A3 (fr) * 2006-12-26 2013-10-23 Sekisui Chemical Co., Ltd. Procédé de mesure du taux d'hémoglobine et de glucose et appareil d'électrophorèse
US10017815B2 (en) 2007-10-30 2018-07-10 Complete Genomics, Inc. Method for high throughput screening of nucleic acids
US9382585B2 (en) 2007-10-30 2016-07-05 Complete Genomics, Inc. Apparatus for high throughput sequencing of nucleic acids
WO2009059022A1 (fr) 2007-10-30 2009-05-07 Complete Genomics, Inc. Appareil pour le séquençage rapide d'acides nucléiques
US9551026B2 (en) 2007-12-03 2017-01-24 Complete Genomincs, Inc. Method for nucleic acid detection using voltage enhancement
US11835437B2 (en) 2011-11-02 2023-12-05 Complete Genomics, Inc. Treatment for stabilizing nucleic acid arrays
US9803239B2 (en) 2012-03-29 2017-10-31 Complete Genomics, Inc. Flow cells for high density array chips
WO2015167990A1 (fr) * 2014-04-29 2015-11-05 Battelle Memorial Institute Injecteurs d'échantillons microfluidiques sans injection électrocinétique
CN114034749A (zh) * 2021-11-09 2022-02-11 鲁东大学 检测多种生物小分子的微型电化学传感器及其制作方法
CN114034749B (zh) * 2021-11-09 2023-09-05 鲁东大学 检测多种生物小分子的微型电化学传感器及其制作方法

Also Published As

Publication number Publication date
US6878255B1 (en) 2005-04-12
AU2249001A (en) 2001-06-06

Similar Documents

Publication Publication Date Title
US6878255B1 (en) Microfluidic devices with thick-film electrochemical detection
US6939451B2 (en) Microfluidic chip having integrated electrodes
Lacher et al. Microchip capillary electrophoresis/electrochemistry
Vandaveer IV et al. Recent developments in amperometric detection for microchip capillary electrophoresis
Hilmi et al. Electrochemical detectors prepared by electroless deposition for microfabricated electrophoresis chips
Wang et al. Microfabricated electrophoresis chips for simultaneous bioassays of glucose, uric acid, ascorbic acid, and acetaminophen
Vandaveer IV et al. Recent developments in electrochemical detection for microchip capillary electrophoresis
Wang Electrochemical detection for capillary electrophoresis microchips: A review
Wang Electrochemical detection for microscale analytical systems: a review
Wang et al. Integrated electrophoresis chips/amperometric detection with sputtered gold working electrodes
Han et al. Fast electrical lysis of cells for capillary electrophoresis
Backofen et al. A chip-based electrophoresis system with electrochemical detection and hydrodynamic injection
Macounová et al. Generation of natural pH gradients in microfluidic channels for use in isoelectric focusing
Lapos et al. Dual fluorescence and electrochemical detection on an electrophoresis microchip
US5399256A (en) Electrochemical detector cell
Wang et al. Microseparation chips for performing multienzymatic dehydrogenase/oxidase assays: simultaneous electrochemical measurement of ethanol and glucose
Costa et al. Microchip electrophoresis and electrochemical detection: a review on a growing synergistic implementation
Wang et al. Capillary Electrophoresis Chips with Thick‐Film Amperometric Detectors: Separation and Detection of Hydrazine Compounds
Wang et al. Microfabricated electrophoresis chip for bioassay of renal markers
US20090178935A1 (en) Miniaturised Biosensor with Optimized Amperometric Detection
Xu et al. Electrochemical detection method for nonelectroactive and electroactive analytes in microchip electrophoresis
Wang et al. Study on the kinetics of homogeneous enzyme reactions in a micro/nanofluidics device
JP2002207031A (ja) マイクロチャンネル型チップ
Wang et al. Thick‐film electrochemical detectors for poly (dimethylsiloxane)‐based microchip capillary electrophoresis
Xu et al. Electrochemical detection modes for microchip capillary electrophoresis

Legal Events

Date Code Title Description
AK Designated states

Kind code of ref document: A1

Designated state(s): AE AG AL AM AT AU AZ BA BB BG BR BY BZ CA CH CN CR CU CZ DE DK DM DZ EE ES FI GB GD GE GH GM HR HU ID IL IN IS JP KE KG KP KR KZ LC LK LR LS LT LU LV MA MD MG MK MN MW MX MZ NO NZ PL PT RO RU SD SE SG SI SK SL TJ TM TR TT TZ UA UG US UZ VN YU ZA ZW

AL Designated countries for regional patents

Kind code of ref document: A1

Designated state(s): GH GM KE LS MW MZ SD SL SZ TZ UG ZW AM AZ BY KG KZ MD RU TJ TM AT BE CH CY DE DK ES FI FR GB GR IE IT LU MC NL PT SE TR BF BJ CF CG CI CM GA GN GW ML MR NE SN TD TG

121 Ep: the epo has been informed by wipo that ep was designated in this application
REG Reference to national code

Ref country code: DE

Ref legal event code: 8642

122 Ep: pct application non-entry in european phase
点击 这是indexloc提供的php浏览器服务，不要输入任何密码和下载